Nanocarriers having surface conjugated peptides and uses thereof for sustained local release of drugs

ABSTRACT

Disclosed are biodegradable nanocarriers that have a net positive surface charge and zeta potential between about +2 to about +20 mV. The positive surface charge of the nanocarriers is provided by peptides that are covalently attached to the surface of the nanocarriers. The nanocarriers may comprise a drug and may be administered for localized and sustained delivery of the drug.

CROSS-REFERENCE TO RELATED PATENT APPLICATIONS

This application claims the benefit of priority to U.S. ProvisionalApplication No. 62/420,344, filed on Nov. 10, 2016, the content of whichis incorporated herein by reference in its entirety. This applicationalso is a continuation-in-part of U.S. patent application Ser. No.15/497,822, filed on Apr. 26, 2017, which application claims the benefitof priority to U.S. Provisional Application No. 62/327,767, filed onApr. 26, 2016, the contents of which are incorporated herein byreference in their entireties.

STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT

This invention was made with government support under R24 EY022883(University of Wisconsin Subcontract to Northwestern University,#457K273) awarded by the National Institutes of Health. The governmenthas certain rights in the invention.

BACKGROUND

The field of the invention relates to compositions and methods forlocalized and sustained delivery of drugs when it is desirable to keepthe drugs confined to a specific body space to enhance their therapeuticaction and minimize cost and non-essential exposure. In particular, thefield of the invention relates to compositions and methods for localizedand sustained delivery of water-soluble synthetic compounds, as well assynthetic lipophilic compounds typically <1,000 Mol. Wt., as well aslocalized and sustained delivery of larger hydrophilic therapeuticagents such as peptides, proteins and nucleic acids.

Major blinding diseases such as exudative “wet” macular degeneration(AMD), and diabetic retinopathy are caused by excessive pathologiccapillary sprouting beneath the retina, damaging retinal layers above.Anti-angiogenic proteins including Avastin, Lucentis and Eyelea, all ofwhich neutralize angiogenic VEGF, slow progress of neovascular eyedisease, but must be injected into patient vitreous humor (VH). VH fillsmost of the eye, is viscous and contains natural polymers with multiplenegative charges. Therapeutic proteins move through and out of the eyewith half-lives of 4-8 days, they must be re-injected at 1-2 monthintervals to sustain efficacy. Frequent injection is a great clinicalburden, is painful, and increases risk of retinal detachment andinfection. Nano-technology involving entrapment or binding of theproteins into transparent degradable particles has been attempted bymany labs seeking continuous release of the injected agent to decreaseinjection frequency, an approach also applied to small synthetic drugs.Typical carriers are large particles (>1 micron), are difficult tosterilize), they move slowly through viscous ocular fluid, or may besmaller and anchored via stable multi (+)charges. Particles may exit theeye intact or may break down to yield fragments which can be toxic orinflammatory, none has yet been approved for the delivery of proteins orpeptides.

SUMMARY

Disclosed are biodegradable nanocarriers having a net positive surfacecharge and zeta potential between about +2 to about +20 mV. The positivesurface charge of the nanocarriers is provided by peptides that arecovalently attached to the surface of the nanocarriers for use asanchoring peptides. The nanocarriers may comprise a non-peptide drug,contained within the carrier, or a peptide drug linked to the carriersimultaneously with the anchoring peptides and may be administered forlocalized and sustained delivery of the drug. The anchoring peptidesthemselves also may include therapeutic peptides, when these arepositively charged through L-Arg content, and attached throughmetastable bonds. Preferably, the anchoring peptides are relativelyshort containing less than about 12 amino acids, safe and non-toxic,non-immunogenic, with net positive charges contributed by 2-4 L-arginineresidues present in each of the anchoring peptides.

The disclosed biodegradable nanocarriers having a net positive surfacecharge and zeta potential between about +2 to about +20 mV adhere topoly-anionic carbohydrates when injected in vivo and thus diffuse slowlyfrom their injection site. As such, the biodegradable nanocarriers maybe injected into tissues comprising poly-anionic carbohydrates, such asvitreous humor or other tissues, and the biodegradable nanocarriers willexhibit slow diffusion from the injected tissue.

The anchor peptides of the biodegradable nanocarriers may be attached tohydroxyl groups present on the surface of the biodegradable nanocarriersvia stable carbamate, leading to slowed diffusion, through multipleionic interactions, in physiological spaces rich in poly-anioniccarbohydrates (e.g. hyaluronic acid or sulfated polysaccharides such asheparinoids, in vitreous humor or other tissue). Alternatively, thepeptides, linked as above, may also contain a metastable bridge formedthrough an amino alcohol which is esterified to a dicarboxylic acidappended to the peptides at their N-terminus. Preferably, the ester bondbetween the amino alcohol and the dicarboxylic acid spontaneouslyhydrolyzes to break down at predictable rates over many weeks or months,which allows the biodegradable nanocarriers, which can be eliminated orbiodegraded, to diffuse from injected tissue more rapidly after mostanchoring peptides are lost through hydrolysis of the ester bond. Therate of this hydrolysis process can be used to tune drug release of adrug that is linked to the nanocarriers via the peptide, by selectingvarious amino-alcohols and dicarboxylic acids for forming the esterbond. As such, the disclosed nanocarriers may be utilized foradministering intra-ocular therapeutics and achieving continuous oculardelivery of both therapeutic proteins and smaller molecules, within orattached to the biodegradable nanocarriers, thus extending time betweenintra-ocular injections.

BRIEF DESCRIPTION OF THE FIGURES

FIG. 1. Schematic drug delivery mechanism. (a) Illustration of particlestructure. Cholesteryl dextran nanoparticle (less than 50 nm indiameter). Hydrophobic domains are inside the particle close to thecore. Particle is illustrated as being labeled by a Rhodamine B aminetracking dye with a density of about 2 molecules per particle. Fourtypes of positively charged peptides are illustrated as being linked onthe particle surface, with a density of about 20 to about 80 peptidesper particle. (b) Illustration of particles within vitreous humor.Vitreous humor is a transparent aqueous gel containing a highlycross-linked collagen fiber-hyaluronic acid (HA). HA molecules areanionic, with random coil structure, fills the space between collagenfibers to prevent aggregation. Nanoparticles (NP) are immobilized by theionic binding between peptides anchored on the particle surface(circles) and hyaluronic acid molecules (strands) in vitreous humor.

FIG. 2. Ex vivo diffusion coefficient measurements in rat vitreous. (a)Relative fluorescence area change as a function of time. (b) Diffusioncoefficient estimated from (a). FL: fluorescence. ζ: Zeta potential,unit mV. The ex vivo nanoparticle diffusion rate of 4-Argpeptide-conjugate (SEQ ID NO.:3) particles are not shown due to theextremely slow particle movement during the observation period. In orderto minimize the influence from initial injection conditions, relativearea changes were used to calculate diffusion rates. a) Nanoparticlesurface modified with peptides containing 1, 2, or 3 L-Arginine groupshad distinct diffusion behaviors where nanoparticles modified with 1-Argpeptides (1R) expanded the fluorescent area quickly, 3-Arg peptide (SEQID NO:2) modified nanoparticles (3R) only diffused minimally in onehour, and the diffusion of 2-Arg peptide (SEQ ID NO:1) modifiednanoparticles (2R) was intermediate. The calculated diffusioncoefficients for 1-Arg, 2-Arg, or 3-Arg peptide modified nanoparticleswere 7.6×10⁻⁹ cm²/s, 2.7×10⁻⁹ cm²/s and 3.0×10⁻¹⁰ cm²/s, respectively.b) ζ: Zeta potential, unit mV.

FIG. 3. In vivo observation of nanoparticle carrier in rat eye.Rhodamine fluorescence images were colored in magenta and overlaid withfundus images. Magenta fluorescence images were overlaid with fundusimages after a 1 ul injection. the 1-Arg nanoparticles spread into a6-mm² area in one day after injection, and 90% of fluorescence signalwas lost by day 8. The 2-Arg nanoparticles (3 d-3f) spread into a 1.7mm² area, and the fluorescence was detectable up to two months. 3-Argnanoparticles (3 g-3i) spread to 1.3 mm², and the fluorescence signalwas only slightly reduced after 6 months. The behavior of 4-Argnanoparticles (not shown) are similar to 3-Arg nanoparticles. Bycomparing the fluorescence locations determined by retinal vasculature,we found that both 2-Arg and 3-Arg nanoparticles stayed approximately atthe original sites of administration.

FIG. 4. In vivo half-life estimation of nanoparticle carriers. (a)Integrated fluorescence intensity of 1-Arg (n=6), 2-Arg (n=5) and 3-Arg(n=3) peptide conjugates as functions of time. Solid black line, dashred line and dash dot blue line are the corresponding exponential decayfittings. (b) Half life time of nanoparticle carriers estimated from(a). Error bar represents 95% confidence interval. The half-life for3-Arg is over 240 days. The monitoring was stopped for terminalhistological toxicity exam.

FIG. 5. Representative histological images. (a), (c), (e), and (g) Wholeeye sections with injections of 1-Arg, 2-Arg, 3-Arg and PBS (controlgroup), respectively. Scale bar: 1 mm. (b), (d), (f) and (h) thecorresponding retinal areas. Scale bar: 50 μm. No tissue or cell damagewas observed compared to PBS vehicle control.

FIG. 6. Peptide conjugates slow diffusion in rabbit vitreous in vivo. 20ul injections of the same 2-Arg (SEQ ID NO:1) or 3-Arg (SEQ ID NO:2)peptide-conjugated carriers with rhodamine label were injected into eyesof 6 New Zealand rabbits on day 1. Two rabbits were euthanized and hadeyes removed and frozen at 1, 2 and 4 weeks. Eyes were cut through whilefrozen, then thawed cold with liquid facing up. Fluorescence wasquantified per eye using an IVIS instrument. Taking 1 week as thezero-time point (100%), 1/3 and 1/20 of the particles were lost after anadditional week, and 1/2 and 1/4 of the fluorescent material was lostafter two more weeks, when zeta potential=2.2 and 4.6 my respectively.

FIG. 7. Schematic of the Cholesterol-dextran nanoparticles testedin-life for rabbit eye clearance. A: Nanoparticle (NP) structure.Hydrophobic domains are at the particle core. B: Particles tagged with<1 mole/NP of Cy7 amine (carbamate-linked) are immobilized in vitreousby ionic binding between peptides on particle surface and hyaluronicacid polymer. Two peptides referred to as either “2-Arg” having twoarginine residues and the amino acid sequence3-pyrrolidine-CONH-PEG(8)-CO-Tyr-Arg-Val-Arg-Ser-NH2 (SEQ ID NO:4), or“3-Arg” having three arginine residues and the amino acid sequence3-pyrrolidine-CONH-PEG(8)-CO-Arg-Arg-Tyr-Arg-Leu-NH₂ (SEQ ID NO:5) werelinked to the nanoparticles.

FIG. 8. Slowed rabbit eye clearance in vivo with Cy7-tagged 3R-peptideCDEX conjugate. 20 μl of anchor peptide amino-PEG8-RRYRL-amide (SEQ IDNO:5) conjugate to CDEX (2.5 mg/ml) along with conjugated 0.05moles/particle Cy7-amine was injected into rabbit eyes on day one. Lefteye 14 peptides/particle, right eye 21peptides/particle. Increasedpeptide load in right eye allows longer residence of conjugate in eye,while left eye has lost >90% of fluorescence.

FIG. 9. Rabbit eye imaging by IVIS. Measurement of number of photons perarea (excitation: 745 nm; emission: 800 nm). A: Left: IVIS scan after 4weeks experiment. Right: IVIS scan after 9 weeks experiment. B: Left:IVIS scan after 4 weeks experiment. Right: IVIS scan after 9 weeksexperiment. 3R peptide conjugate (SEQ ID NO:5) is seen to be retainedlonger in the eye compared with 2R peptide (SEQ ID NO:4) conjugate atsimilar peptide loading.

FIG. 10. In vivo charge and zeta potential-dependent loss of NP fromrabbit vitreous expressed as a percentage of the first measured photonflux at day 10 post-injection (taken as day 0). Volume of injection: 25μl; nanocarrier concentration: 3 mg/ml. [Control: CDEX70-0: (n=2).CDEX70-2R; 64 peptides per particle by BCA (n=3) and CDEX70-3R; 61peptides per particle by BCA (n=3)]. Half-lives: CDEX-0: 4 days;CDEX-2R: 7 days; CDEX70-3R: 13 days. 2R and 3R peptides are respectively(SEQ ID NO:4) and (SEQ ID NO:5) linked as carbamates of3pyrrolidineCO-amido-PEG8-CO-peptide to Cy7-CDEX70. Cy7 amine iscarbamate-linked at <1 mole/mole NP.

FIG. 11. Initial dose dependence of in vivo loss of NP from rabbitvitreous expressed as percentage fluorescent photon flux compared to thefirst measurement at day 10 post-injection of 20 ul (taken as day 0) ofCDEX70-2R₆₄-Cy7 at 4 different concentrations [Control: 0 mg/ml (n=6). 3mg/ml (n=3). 6 mg/ml (n=2) and 12 mg/ml (n=2)]. This indicatesconsistent slowing of nanoparticle loss up to 120 μg injected 2Rconjugates, but large initial loss, implying binding capacity isexceeded at 240 μg in 2 ml rabbit eye.

FIG. 12A. Survival curve for mice bearing peritoneal ID8 mouse ovariantumor administered IP, QD of bioactive 2R anti-tumor nonapeptide, vs.vehicle starting day 22 after tumor inoculation(adipic-Sar-Tyr-Asn-Leu-Tyr-Arg-Val-Arg-Ser-NH₂) (SEQ ID NO:6).

FIG. 12B. Retinal protective activity of the same peptide is seen inreduction of laser-induced choroidal neovascularization (CNV), a modelof neovascular macular degeneration. A single injection of 1-ul 4 mg/mlpeptide (SEQ ID NO:6) or control is injected into mouse vitreous 2 daysbefore laser wounding of the retina. Angiogenesis markers are detectedby antibody stain, 14 days later.

FIG. 13. Bioactive SEQ ID NO:6 (FIG. 12A, B) is linkable to CDEX as3-pyrrolidinol ester prodrug. The bridged prodrug linking form ofbioactive peptide (SEQ ID NO:6) and its attachment to CDEX is detailedherein. 44 mg/ml conjugate containing 76 uM linked peptide was incubatedin HEPES buffer, pH7.4 at 37° C. At 0, 3 and 7 day time pointsfilterable peptide (10 kD MWCO) centrifugal filter was identified as SEQID NO:6 by HPLC and quantified by UV spectrum of the filtrate, where 100uM peptide has peak OD=0.22 at 276 nM. A semi-log loss curve showshalf-life of 28 days, releasing bioactive peptide at approximately 2%per day of the NP-bound amount.

DETAILED DESCRIPTION

The present invention is described herein using several definitions, asset forth below and throughout the application.

Unless otherwise specified or indicated by context, the terms “a”, “an”,and “the” mean “one or more.” For example, “a nanocarrier” and “apeptide” should be interpreted to mean “one or more. nanocarriers” and“one or more peptides,” respectively.

As used herein, “about,” “approximately,” “substantially,” and“significantly” will be understood by persons of ordinary skill in theart and will vary to some extent on the context in which they are used.If there are uses of these terms which are not clear to persons ofordinary skill in the art given the context in which they are used,“about” and “approximately” will mean plus or minus <10% of theparticular term and “substantially” and “significantly” will mean plusor minus >10% of the particular term.

As used herein, the terms “include” and “including” have the samemeaning as the terms “comprise” and “comprising.” The terms “comprise”and “comprising” should be interpreted as being “open” transitionalterms that permit the inclusion of additional components further tothose components recited in the claims. The terms “consist” and“consisting of” should be interpreted as being “closed” transitionalterms that do not permit the inclusion of additional components otherthan the components recited in the claims. The term “consistingessentially of” should be interpreted to be partially closed andallowing the inclusion only of additional components that do notfundamentally alter the nature of the claimed subject matter.

As used herein, a “patient” may be interchangeable with “subject” or“individual” and means an animal, which may be a human or non-humananimal, in need of treatment. Non-human animals may include dogs, cats,horses, cows, pigs, sheep, and the like.

A “patient in need thereof” may include a patient having or at risk fordeveloping an eye disease. The presently disclosed peptides, prodrugs,and pharmaceutical compositions may be utilized to treat eye diseasesthat are characterized by neovascular retinal disease, such as maculardegeneration, and that may be treated with anti-angiogenic agents. Thepresently disclosed peptides, prodrugs, and pharmaceutical compositionsmay be utilized to treat eye diseases such as diabetic retinopathy. Thepresently disclosed peptides, prodrugs, and pharmaceutical compositionsmay be utilized to treat eye diseases by administering peptide, ornon-peptide drugs or prodrugs by intravitreal injection of the disclosedpeptide-anchored carriers.

A “patient in need thereof” may include a patient having maculardegeneration. Macular degeneration is a medical condition predominantlyfound in elderly adults in which the center of the retina of the eye,otherwise known as the “macula” area of the retina, exhibits thinning,atrophy, and sometimes new blood vessel formation. Although maculardegeneration sometimes may affect younger individuals, the termgenerally refers to “age-related” macular degeneration (i.e., “AMD” or“ARMD”). Advanced AMD has two forms referred to as the “dry” and “wet”forms. The dry form of advanced AMD is characterized by centralgeographic atrophy, which causes vision loss through the loss ofphotoreceptors in the central part of the eye (i.e., rods and cones).The wet form of advanced AMD, otherwise referred to as “neovascular” or“exudative” AMD, causes vision loss due to abnormal blood vessel growthin the choriocapillaris, through a retinal layer referred to as “Bruch'smembrane.” The wet form of AMD ultimately leads to blood and proteinleakage below the macula. This bleeding, leaking, and scarring below themacula eventually cause irreversible damage to the photoreceptors andrapid vision loss if left untreated. Until recently, no effectivetreatments were known for wet macular degeneration. However, new drugsthat inhibit angiogenesis (i.e., “anti-angiogenic agents”) have beenshown to cause regression of the abnormal blood vessels and improvementof vision. In order to be effective, anti-angiogenic agents must beinjected directly into the vitreous humor of the eye. The duration ofeffectiveness of such injections is impractically short for smallpeptides unless the latter are continuously released from a carriermacromolecule, or nanocarrier, for which ester linkage providescontrolled rates of release.

The compositions disclosed herein may include nanocarriers. As usedherein, the term “nanocarrier” may be used interchangeably with theterms “nanoparticle” and “nanoparticle carrier” and may refer to a solidparticle, a semi-solid particle and/or a colloidal particle (e.g., a gelor hydrogel). The nanocarriers disclosed herein preferably have aneffective diameter of less than about 1 micron, 900 nm, 800 nm, 700 nm,600 nm, 500 nm, 400 nm, 300 nm, 200 nm, 100 nm or less, or thenanocarriers have an effective diameter within a range bounded by any ofthese values (e.g., 5-50 nm or 100-200 nm).

The disclosed nanocarriers preferably are transparent, for example asmeasured by total transmittance for use in the eye. Preferably, thenanocarriers disclosed herein may absorb and reflect less than about10%, 9%, 8%, 7%, 6%, 5%, 4%, 3%, 2%, or 1% of incident light and/or mayhave a total transmittance of at least about 90%, 91%, 92%, 93%, 94%,95%, 96%, 97%, 98%, or 99% of incident light. As such, the nanocarriersdisclosed herein may comprise a polymeric material that absorbs andreflects less than about 10%, 9%, 8%, 7%, 6%, 5%, 4%, 3%, 2%, or 1% ofincident light and/or has a total transmittance of at least about 90%,91%, 92%, 93%, 94%, 95%, 96%, 97%, 98%, or 99% of incident light.Preferably, the nanocarriers remain transparent after the nanocarriersare injected into the vitreous humor. Transparency may not be requiredfor use outside the eye.

The disclosed nanocarriers preferably are biodegradable and/or can besafely eliminated through the kidney or alimentary tract. As usedherein, “biodegradable” describes a material, such as a polymer, that iscapable of being degraded in a physiological environment into smallerbasic components. Preferably, the smaller basic components areinnocuous. For example, a biodegradable polymer may be degraded intobasic components that include, but are not limited to, water, carbondioxide, sugars, organic acids (e.g., tricarboxylic or amino acids), andalcohols (e.g., glycerol or polyethylene glycol). Biodegradablematerials may include polymeric carbohydrates. Biodegradable materials(including polymers) that may be utilized to prepare the nanocarrierscontemplated herein may include materials disclosed in U.S. Pat. Nos.7,470,283; 7,390,333; 7,128,755; 7,094,260; 6,830,747; 6,709,452;6,699,272; 6,527,801; 5,980,551; 5,788,979; 5,766,710; 5,670,161; and5,443,458; and U.S. Published Application Nos. 20090319041; 20090299465;20090232863; 20090192588; 20090182415; 20090182404; 20090171455;20090149568; 20090117039; 20090110713; 20090105352; 20090082853;20090081270; 20090004243; 20080249633; 20080243240; 20080233169;20080233168; 20080220048; 20080154351; 20080152690; 20080119927;20080103583; 20080091262; 20080071357; 20080069858; 20080051880;20080008735; 20070298066; 20070288088; 20070287987; 20070281117;20070275033; 20070264307; 20070237803; 20070224247; 20070224244;20070224234; 20070219626; 20070203564; 20070196423; 20070141100;20070129793; 20070129790; 20070123973; 20070106371; 20070050018;20070043434; 20070043433; 20070014831; 20070005130; 20060287710;20060286138; 20060264531; 20060198868; 20060193892; 20060147491;20060051394; 20060018948; 20060009839; 20060002979; 20050283224;20050278015; 20050267565; 20050232971; 20050177246; 20050169968;20050019404; 20050010280; 20040260386; 20040230316; 20030153972;20030153971; 20030144730; 20030118692; 20030109647; 20030105518;20030105245; 20030097173; 20030045924; 20030027940; 20020183830;20020143388; 20020082610; and 0020019661; the contents of which areincorporated herein by reference in their entireties. Materials that maybe safely eliminated through the kidney may include, but are not limitedto, dextran 40 and dextran 70.

As used herein, the term “peptide” refers to a polymer of amino acidresidues joined by amide linkages. The term “amino acid residue,”includes but is not limited to amino acid residues contained in thegroup consisting of alanine (Ala or A), cysteine (Cys or C), asparticacid (Asp or D), glutamic acid (Glu or E), phenylalanine (Phe or F),glycine (Gly or G), histidine (His or H), isoleucine (Ile or I), lysine(Lys or K), leucine (Leu or L), methionine (Met or M), asparagine (Asnor N), proline (Pro or P), glutamine (Gln or Q), arginine (Arg or R),serine (Ser or S), threonine (Thr or T), valine (Val or V), tryptophan(Trp or W), and tyrosine (Tyr or Y) residues. The term “amino acidresidue” also may include amino acid residues contained in the groupconsisting of homocysteine, 2-Aminoadipic acid, N-Ethylasparagine,3-Aminoadipic acid, Hydroxylysine, β-alanine, β-Amino-propionic acid,allo-Hydroxylysine acid, 2-Aminobutyric acid, 3-Hydroxyproline,4-Aminobutyric acid, 4-Hydroxyproline, piperidinic acid, 6-Aminocaproicacid, Isodesmosine, 2-Aminoheptanoic acid, allo-Isoleucine,2-Aminoisobutyric acid, N-Methylglycine (sarcosine), 2-Aminoisobutyricacid, N-methyl-2-aminoisobutyric acid, N-Methylisoleucine,2-Aminopimelic acid, 6-N-Methyllysine, 2,4-Diaminobutyric acid,N-Methylvaline, Desmosine, Norvaline, 2,2′-Diaminopimelic acid,Norleucine, 2,3-Diaminopropionic acid, Ornithine, and N-Ethylglycine.Typically, the amide linkages of the peptides are formed from an aminogroup of the backbone of one amino acid and a carboxyl group of thebackbone of another amino acid.

In some embodiments, the disclosed peptides may comprise two or moreamino acids which optionally may be charged or uncharged atphysiological pH. Typically, positively charged amino acids of thepeptide at physiological pH include, L-arginine, and lysine, withpartial+charge found in histidine. Typically, negatively charged aminoacids at physiological pH include aspartic acid and glutamic acid. Theremaining amino acids, other than these positively charged andnegatively charged amino acids, typically are neutral at physiologicalpH. L-arginine is the predominant or sole source of charge in anchorpeptides used here. The minimum net charge of each our peptides, whencovalently linked to carrier is +2, the maximum net charge of each being+4.

As used herein, a peptide is defined as a short polymer of amino acids,of a length typically of 20 or less amino acids, and more preferred is alength of less than 12 amino acids (Garrett & Grisham, Biochemistry,2^(nd) edition, 1999, Brooks/Cole, 110). In some embodiments, a peptideas contemplated herein may include no more than about 2, 3, 4, 5, 6, 7,8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, or 20 amino acids. Apolypeptide, also referred to as a protein, is typically of length >100amino acids (Garrett & Grisham, Biochemistry, 2^(nd) edition, 1999,Brooks/Cole, 110). Peptides or protein agents to be delivered maysimultaneously be attached on the carriers to which the smalleranchoring peptides are conjugated.

The peptides disclosed herein may be modified to include non-amino acidmoieties. Modifications may include but are not limited to carboxylation(e.g., N-terminal carboxylation via addition of a di-carboxylic acidhaving 4-8 straight-chain or branched carbon atoms, such as glutaricacid, succinic acid, adipic acid, suberic acid and 4,4-dimethylglutaricacid), amidation (e.g., C-terminal amidation via addition of an amide orsubstituted amide such as alkylamide or dialkylamide), PEGylation,including amino-PEGylation (e.g., N-terminal or C-terminal PEGylationvia amide bonds), acylation (e.g., N-acylation (amides) with alpha,beta, gamma, delta, or epsilon amino acids. In addition, N-terminalamino-PEG-peptide may be further capped as an amino-PEG amide with3-pyrrolidine carboxylic acid or 3-pyrrolidyine-amido-succininc acidwhereby the appended pyrrolidine amino group can form the carbamate linkto dextran OH groups.

The disclosed peptides may exhibit one or more biological functionsincluding anti-angiogenic activity. Methods for measuringanti-angiogenic activity are disclosed herein and are known in the art.

The disclosed peptides may be synthesized by any technique known tothose of skill in the art and by methods as disclosed herein. Methodsfor synthesizing the disclosed peptides may include chemical synthesisof proteins or peptides, the expression of peptides through standardmolecular biological techniques, and/or the isolation of proteins orpeptides from natural sources. The disclosed peptides thus synthesizedmay be subject to further chemical and/or enzymatic modification.Various methods for commercial preparations of peptides and polypeptidesare known to those of skill in the art.

Reference is made herein to peptides, polypeptides and pharmaceuticalcompositions comprising peptides and polypeptides. Exemplary peptidesand polypeptides may comprise, consist essentially of, or consist of theamino acid sequence of any of SEQ ID NOs:1-20, or variants of thepeptides and polypeptides may comprise, consist essentially of, orconsist of an amino acid sequence having at least about 80%, 90%, 95%,96%, 97%, 98%, or 99% sequence identity to any of SEQ ID NOs:1-20.Variant peptides polypeptides may include peptides or polypeptideshaving one or more amino acid substitutions, deletions, additions and/oramino acid insertions relative to a reference peptide or polypeptide.Preferably, in order to minimize immunogenicity and toxicity, anchoringpeptides utilized here are small (<12 amino acids), and contain no fewerthan 2 L-Arg and no more than 4 L-Arg in which the amino acid sequenceis identical to or closely resembles naturally occurring human proteinsequences found in intercellular matrix or in body fluids such as urineor plasma. Thus no more than one amino acid internally and no more thanone N-terminal appended amino acid typically varies from the naturalhuman sequence.

The amino acid sequences contemplated herein may include conservativeamino acid substitutions relative to a reference amino acid sequence.For example, a variant peptide or polypeptide as contemplated herein mayinclude conservative amino acid substitutions relative to a referencepeptide or polypeptide. “Conservative amino acid substitutions” arethose substitutions that are predicted to interfere least with theproperties of the reference polypeptide. In other words, conservativeamino acid substitutions substantially conserve the structure and thefunction of the reference protein. The following table provides a listof exemplary conservative amino acid substitutions.

Original Residue Conservative Substitution Ala Gly, Ser Arg His, Lys AsnAsp, Gln, His Asp Asn, Glu Cys Ala, Ser Gln Asn, Glu, His Gln Asp, Gln,His Gly Ala His Asn, Arg, Gln, Glu Ile Leu, Val Leu Ile, Val Lys Arg,Gln, Glu Met Leu, Ile Phe His, Met, Leu, Trp, Tyr Ser Cys, Thr Thr Ser,Val Trp Phe, Tyr Tyr His, Phe, Trp Val Ile, Leu, Thr

Conservative amino acid substitutions generally maintain (a) thestructure of the peptide or polypeptide backbone in the area of thesubstitution, for example, as a beta sheet or alpha helicalconformation, (b) the charge or hydrophobicity of the molecule at thesite of the substitution, and/or (c) the bulk of the side chain.

Variants comprising deletions relative to a reference amino acidsequence are contemplated herein. A “deletion” refers to a change in theamino acid or nucleotide sequence that results in the absence of one ormore amino acid residues or nucleotides relative to a referencesequence. A deletion may remove at least 1, 2, 3, 4, 5, 10, 20, 50, 100,or 200 amino acids residues or nucleotides. A deletion may include aninternal deletion or a terminal deletion (e.g., an N-terminal truncationor a C-terminal truncation of a reference polypeptide or a 5′-terminalor 3′-terminal truncation of a reference polynucleotide).

“Homology” refers to sequence similarity or, interchangeably, sequenceidentity, between two or more polypeptide sequences. Homology, sequencesimilarity, and percentage sequence identity may be determined usingmethods in the art and described herein.

The phrases “percent identity” and “% identity,” as applied topolypeptide sequences, refer to the percentage of residue matchesbetween at least two polypeptide sequences aligned using a standardizedalgorithm. Methods of polypeptide sequence alignment are well-known.Some alignment methods take into account conservative amino acidsubstitutions. Such conservative substitutions, explained in more detailabove, generally preserve the charge and hydrophobicity at the site ofsubstitution, thus preserving the structure (and therefore function) ofthe polypeptide. Percent identity for amino acid sequences may bedetermined as understood in the art. (See, e.g., U.S. Pat. No.7,396,664, which is incorporated herein by reference in its entirety). Asuite of commonly used and freely available sequence comparisonalgorithms is provided by the National Center for BiotechnologyInformation (NCBI) Basic Local Alignment Search Tool (BLAST) (Altschul,S. F. et al. (1990) J. Mol. Biol. 215:403 410), which is available fromseveral sources, including the NCBI, Bethesda, Md., at its website. TheBLAST software suite includes various sequence analysis programsincluding “blastp,” that is used to align a known amino acid sequencewith other amino acids sequences from a variety of databases.

A “variant” of a particular polypeptide sequence may be defined as apolypeptide sequence having at least 50% sequence identity to theparticular polypeptide sequence over a certain length of one of thepolypeptide sequences using blastp with the “BLAST 2 Sequences” toolavailable at the National Center for Biotechnology Information'swebsite. (See Tatiana A. Tatusova, Thomas L. Madden (1999), “Blast 2sequences—a new tool for comparing protein and nucleotide sequences”,FEMS Microbiol Lett. 174:247-250). Such a pair of polypeptides may show,for example, at least 60%, at least 70%, at least 80%, at least 90%, atleast 91%, at least 92%, at least 93%, at least 94%, at least 95%, atleast 96%, at least 97%, at least 98%, or at least 99% or greatersequence identity over a certain defined length of one of thepolypeptides. A “variant” may have substantially the same functionalactivity as a reference polypeptide. For example, a variant may exhibitor more biological activities associated with PEDF. “Substantiallyisolated or purified” nucleic acid or amino acid sequences arecontemplated herein. The term “substantially isolated or purified”refers to nucleic acid or amino acid sequences that are removed fromtheir natural environment, and are at least 60% free, preferably atleast 75% free, and more preferably at least 90% free, even morepreferably at least 95% free from other components with which they arenaturally associated.

A “composition comprising a given polypeptide” refers broadly to anycomposition containing the given amino acid sequence. The compositionmay comprise a dry formulation or an aqueous solution. The compositionsmay be stored in any suitable form including, but not limited to,freeze-dried form and may be associated with a stabilizing agent such asa carbohydrate. The compositions may be aqueous solution containingsalts (e.g., NaCl), detergents (e.g., sodium dodecyl sulfate; SDS), andother components (e.g., Denhardt's solution, dry milk, salmon sperm DNA,and the like).

The disclosed pharmaceutical composition may comprise the disclosedpeptides, polypeptides, and variants at any suitable dose. Suitabledoses may include, but are not limited to, about 0.01 μg/dose, about0.05 μg/dose, about 0.1 μg/dose, about 0.5 μg/dose, about 1 μg/dose,about 2 μg/dose, about 3 μg/dose, about 4 μg/dose, about 5 μg/dose,about 10 μg/dose, about 15 μg/dose, about 20 μg/dose, about 25 μg/dose,about 30 μg/dose, about 35 μg/dose, about 40 μg/dose, about 45 μg/dose,about 50 μg/dose, about 100 μg/dose, about 200 μg/dose, about 500μg/dose, or about 1000 μg/dose. In some embodiments, these contemplateddoses may be administered intravitreally, intracranially, and/orintraperitoneally.

The disclosed peptides, polypeptides, or variants thereof may beadministered at any suitable dose level. In some embodiments, a subjectin need thereof is administered a peptide, polypeptide, or variantthereof at a dose level of from about 1 ng/kg up to about 1 mg/kg. Insome embodiments, the peptide, polypeptide, or variant thereof isadministered to the subject in need thereof at a dose level of at leastabout 1 ng/kg, 2 ng/kg, 5 ng/kg, 10 ng/kg, 20 ng/kg, 50 ng/kg, 100ng/kg, 200 ng/kg, 500 ng/kg, 1 μg/kg, 2 μg/kg, 5 μg/kg, 10 μg/kg, 20μg/kg, 50 μg/kg, 100 μg/kg, 200 μg/kg, 500 μg/kg, or 1 mg/kg. In otherembodiments, the peptide, polypeptide, or variant thereof isadministered to the subject in need thereof at a dose level of less thanabout 1 mg/kg, 500 μg/kg, 200 μg/kg, 100 μg/kg, 50 μg/kg, 20 μg/kg, 10μg/kg, 5 μg/kg, 2 μg/kg, 1 μg/kg, 500 ng/kg, 200 ng/kg, 100 ng/kg, 50ng/kg, 20 ng/kg, 10 ng/kg, 5 ng/kg, 2 ng/kg, or 1 ng/kg. In furtherembodiments, the peptide, polypeptide, or variant thereof isadministered to a subject in need thereof within a dose level rangebounded by any 1 ng/kg, 2 ng/kg, 5 ng/kg, 10 ng/kg, 20 ng/kg, 50 ng/kg,100 ng/kg, 200 ng/kg, 500 ng/kg, 1000 ng/kg, 2000 ng/kg, or 5000 ng/kg.

The disclosed peptides, polypeptides, or variants thereof may beadministered under any suitable dosing regimen. Suitable dosing regimensmay include, but are not limited to, once every week, once every month,once every two months, once every three months, once every four months,once every 5 months, or once every 6 months.

The peptides and prodrugs utilized in the methods disclosed herein maybe formulated as a pharmaceutical composition for delivery via anysuitable route (e.g. parenteral or intravitreal routes). As such,pharmaceutical compositions comprising the peptides and prodrugs may beadapted for administration by any appropriate route, for exampleintravitreal or intraperitoneal, or intracranial or intra-articular withthe intention of local confinement, and parenteral (includingsubcutaneous, intramuscular, intravenous or intradermal) route. Suchformulations may be prepared by any method known in the art of pharmacy,for example by bringing into association the active ingredient withsuitable carrier(s) or excipient(s). In some embodiments, the prodrugcarrier-bound forms described herein may be intended for less frequentdosing ranging from once weekly to once monthly to once per 2 months orless frequently. Pharmaceutical compositions adapted for parenteraladministration include aqueous and non-aqueous sterile injectionsolutions which may contain anti-oxidants, buffers, bacteriostats andsolutes which render the formulation isotonic with bodily fluid of theintended recipient; and aqueous and non-aqueous sterile suspensionswhich may include suspending agents and thickening agents. Theformulations may be presented in unit-dose or multi-dose containers, forexample sealed ampoules and vials, and may be stored in a freeze-dried(lyophilized) condition requiring only the addition of the sterileliquid carrier, for example water for injections, immediately prior touse. Formulations may contain excess hyaluronic acid or other naturallyoccurring poly-anionic carbohydrates as excipients intended toimmobilize and slow diffusion of the cationic nanoparticles, to minimizetoxicity and extend continuous release.

The nanocarriers disclosed herein may be formulated as pharmaceuticalcompositions for use in treating and/or preventing diseases or disordersthat are amenable to treatment by anti-angiogenic agents. As such, thepharmaceutical compositions may be administered to a patient in order toinhibit angiogenesis.

The disclosed methods may include administering to a patient aneffective amount of a pharmaceutical composition to treat and/or preventa disease and/or disorder. As used herein, the phrase “effective amount”shall mean that drug dosage that provides the specific pharmacologicalresponse for which the drug is administered in a significant number ofpatients in need of such treatment. An effective amount of a drug thatis administered to a particular patient in a particular instance willnot always be effective in treating the conditions/diseases describedherein, even though such dosage is deemed to be a therapeuticallyeffective amount by those of skill in the art.

The disclosed methods may include administering to a patient aneffective amount of a pharmaceutical composition for inhibitingangiogenesis relative to a control. In some embodiments, angiogenesisand/or tumorigenesis is inhibited by at least 10%, at least 25%, atleast 50%, at least 75%, at least 90%, or at least 95% in a treatedsample relative to an untreated control sample.

Nanocarriers Having Surface Conjugated Peptides and Uses Thereof forSustained Local Release of Drugs

Disclosed are nanocarriers that are biodegradable, that are transparent,that have an average effective diameter of less than about 200 nm(preferably between 5-50 nm) and that have a net positive surface chargeand zeta potential between about +2 to about +9, +10, +11, +12, +13,+14, +15, +16, +17, +18, +19, or +20 mV. The positive surface charge ofthe nanocarriers is provided by peptides that are covalently attached tothe surface of the nanocarriers. Larger zeta potential (up to +20 mV)may be used for confinement in body cavities having lower concentrationsof poly-anionic carbohydrate than found in vitreous, or in moreliquefied geriatric vitreous, or where purified hyaluronic acid (HA) isused as a medium (formulation) for the delivery of peptide-conjugatedcarriers.

In some embodiments, the nanocarriers may include a core comprising apolymeric carbohydrate material. Suitable materials for the nanocarriersmay include, but are not limited to, dextran which optionally is acondensed dextran hydrogel, chitosan, pullulan, or a dendrimer. The corematerial of the nanocarriers preferably includes hydroxyl groups and/orcarboxyl groups on the surface of the core material of the nanocarriers.In some embodiments, the nanocarriers comprise dendrimers havingterminal hydroxyl groups and/or terminal carboxyl groups. In furtherembodiments, the carriers comprise dextran and/or hyaluronic acid, andoptionally the dextran or hyaluronic acid is crosslinked and/orcondensed. Nanoparticulate carriers as disclosed in the art, in someinstances, may be modified to prepare nanocarriers as disclosed herein.(See, e.g., Araujo et al., Nanomedicine 8 (2012) 1034-1041; Park et al.,Diabetes 58 (2009) 1902-1913; Jin et al., Inest. Ophthalmol. Vis. Sci.52 (2011) 6230-6237; Liu et al., Invest Ophthalmol. Vis. Sci. 52 (2011)4789-4794; Pepic et al., J. Pharm. Sci. 99 (2010) 4317-4325; Marano etal., Gen Ther. 12 (2005) 1544-1550; and Marano et al., Exp. Eye Res. 79(2004) 525-535; the contents of which are incorporated herein byreference in their entireties). Polylactide (PLA) nanocarriers, poly(lactic-co-glycolic acid) (PLGA) nanocarriers, PLA/PLGA nanocarriers,and derivatives thereof may be modified to prepare nanocarriers ascontemplated herein. Polyamidoamine (PAMAM) dendrimer nanocarriers andderivatives thereof may be modified to prepare nanocarriers ascontemplated herein. Dextran nanocarriers, derivatives thereof, andhydrogels thereof may be modified to prepare nanocarriers ascontemplated herein. Cholesterol-modified or lipid-modified dextran andhydrogels thereof may be modified to prepare nanocarriers ascontemplated herein (e.g., dextran polymers to which cholesterol orstearic amine has been conjugated to 0.5%, 1%, 2%, 3%, 4%, 5%, 6%, 7%,8%, 9%, or 10% (or a percentage range bounded by any of 0.5%, 1%, 2%,3%, 4%, 5%, 6%, 7%, 8%, 9%, or 10%) of the sugar monomers of dextran).In nanocarriers comprising cholesterol-modified dextran, preferably theattached cholesterol forms a core, thereby condensing the dextranpolymer into a compact sphere. A cholesterol core may be substituted byother lipohilic compounds such as stearylamine. Such particle cores, inaddition to making the carriers more compact, may be used to containsynthetic lipophilic drugs for delivery, while surface-linked peptidesprolong overall intravitreal residence.

The disclosed nanocarriers include peptides conjugated to the surface ofthe nanocarriers. The disclosed peptides typically are small andcomprise at least 2 amino acids and no more than 11 amino acids. In someembodiments, the disclosed nanocarriers comprise at least 5, 10, 15, 20,25, 30, 40, 50, 60, 70 or 80 peptides per 70-100 kD nanocarrier (or thenanocarriers comprise a range of peptides bounded by any of 5, 10, 15,20, 25, 30, 40, 50, 60, 70 or 80 peptides per particle (e.g., 15-35peptides per nanocarrier)) where the full sized carrier-peptideconjugate has molecular weight ranging from 20 kD to 200 kD.

The disclosed peptides may comprise an amino acid sequence that isselected in order to provide a suitable surface charge to thenanocarriers to which the peptides are conjugated. In some embodiments,the amino acid sequence of the peptides includes at least 2 L-Arginineresidues, no more than 4 L-Arginine residues, and preferably no othercharged amino acids other than L-Arginine residues, excluding aminesthat may be used in linking the peptides to the nanocarriers. As such,the peptides may provide a positive net charge to the surface of thenanocarriers.

The disclosed peptides may comprise an amino acid sequence that isselected in order to minimize any immune response against the peptides.In some embodiments, the disclosed peptides may comprise an amino acidsequence that is found in a human protein. In some embodiments, thedisclosed peptides comprise an amino acid sequence of a human proteinthat is secreted into the extracellular matrix or that is found invitreous humor, blood, urine, or saliva. Suitable amino acid sequencesfor the disclosed peptides may include, but are not limited to, aminoacid sequences found in human thrombospondin, pigment epithelium-derivedfactor (PEDF), alpha A crystallin, heat shock protein 20, lamininreceptor, circulating fibrin peptides, and protamines. To furtherminimize immunogenicity or instability PEG amines from molecular weight200 to 2000 may be appended as amides to the C-termini of anchoringpeptides, or amino-PEG-carboxylates may be appended to the peptide asN-terminal amides, so that N-terminal amino groups can be linked, ascarbamates or amides to the carrier surface to shield anchoring peptidesfrom the immune system or from degradative enzymes.

In some embodiments, the disclosed peptides may comprise an amino acidsequence of pigment epithelium-derived factor (PEDF) or a modified aminoacid sequence of PEDF. Modified PEDF peptides that may be suitable foruse in the present application may include modified PEDF peptidesdisclosed in U.S. Published Application No. 2017-0305998, published onOct. 26, 2017, the content of which is incorporated herein by referencein its entirety.

The disclosed peptides may be modified. In some embodiments, thedisclosed peptides have C-terminal amide or ethylamide groups,PEG(4-12)-amide groups, or 3-pyrrolidine-carboxamido-PEG(4-12) groups.

The disclosed peptides may be further modified to include anon-naturally occurring amino acid at their N-terminus. In someembodiments, the peptides include at their N-terminus a neutral aminoacid residue selected from the group consisting of sarcosine,beta-alanine, 2-amino-isobutyric acid or N-methyl-2-aminoisobutyricacid. The disclosed peptides also may contain between 1 and 2 modifiedamino acids internally, provided that the overall sequence is at least75% identical to that within a human protein.

The disclosed peptides typically are covalently conjugated to a hydroxylgroup present on the surface of the nanocarriers. In some embodiments,the peptides are covalently attached to the nanocarriers via conjugationbetween hydroxyl groups on the surface of the nanocarriers and freeamino groups on the peptides. Suitable amino groups on the peptides forcovalent attachment may include, but are not limited to free alpha aminogroups on the peptides, free beta amino groups on the peptides, or freeamino groups present in an N-terminal moiety of the peptides, such as alinker moiety which may be referred to as “B.” Optionally, linker B isselected from the group consisting of amino-n-butoxy,amino-ethoxyethyloxy, amino-piperidyl (3, or 4)-oxy, amino-pyrrolidinyl(3)-oxy, amino-benzyl (3, or 4)-oxy, aminoethylamido-valeric acid(4)-oxy, amino-cyclohexyl (3, or 4)-oxy, and amino-cyclopentyl (3)-oxy.Suitable amino groups may be present in an N-terminal moiety of thepeptides, such as an amino-PEG-acyl group, or an epsilon amino caproylgroup.

In some embodiments, the peptides of the disclosed nanocarriers may havea formula: B-Z-AA0-AA1-AA2-AA3-AA4-AA5-AA6-AA7-AA8-AA9-AA10-Y, wherein:B is present or absent, and when B is present, B is selected from thegroup consisting of amino-n-butoxy, amino-ethoxyethyloxy,amino-piperidyl (3, or 4)-oxy, amino-pyrrolidinyl (3)-oxy, amino-benzyl(3, or 4)-oxy, aminoethylamido-valeric acid (4)-oxy, amino-cyclohexyl(3, or 4)-oxy, and amino-cyclopentyl (3)-oxy; Z is absent or present,and when Z is present, Z is amino-PEG-carboxylic acid (optionallyincluding 4-16 ethylene glycol units) in amide bond to AA0 or AA1; AA0is present or absent, and when present, AA0 is selected from the groupconsisting of L-arginine, a naturally occurring amino acid with anuncharged side chain (e.g., sarcosine and glycine), and beta-alanine;AA1, AA2, AA3, AA4, AA5, AA6, AA7, AA8, AA9, and AA10 each individuallyare present or absent, and when present are individually selected fromL-arginine or a naturally occurring amino acid with an uncharged sidechain; Y is an amide, a mono-substituted or di-substituted alkyl amide(e.g., methylamide, ethylamide, and dimethylamide), or a PEG(4-12)amide;with the proviso that: the peptides have a net positive charge and zetapotential between about +2 to about +9, +10, +11, +12, +13, +14, +15,+16, +17, +18, +19, or +20 mV; the peptides comprise at least 2 aminoacids and no more than 11 amino acids; and the amino acid sequence ofthe peptides includes at least 2 L-Arginine residues, no more than 4L-Arginine residues, and no other charged amino acids other thanL-Arginine residues.

In some embodiments the carrier polymer is a highly carboxylatedcarbohydrate such as hyaluronic acid to which the peptide-bridging groupB is linked via and amide bond to the carrier carboxyl groups. In orderto achieve the required positive zeta potentials described herein forslowed vitreal diffusion such embodiment requires sufficient capping ofthe excess unlinked carboxyl groups to allow a net positive charge onthe conjugated surface. This may be achieved by linkingPEG(4-24)-amines, as amides, to 20% or 50% or >80% of the remaining freecarboxyl groups, the attached PEG groups can also shield the conjugatedanchoring peptides from degradative enzymes and from the immune system.

In some embodiments of the disclosed nanocarriers, the peptides arecovalently attached to the nanocarriers via conjugation between hydroxylgroups on the surface of the nanocarriers and free carboxyl groups onthe peptides (e.g., via an ester linkage). The peptides of the disclosednanocarriers may have a formula:Z-AA0-AA1-AA2-AA3-AA4-AA5-AA6-AA7-AA8-AA9-AA10-Y, wherein Z isdicarboxylic acid in half-amide bond with AA0 or AA1 (e.g., where Z issuberic acid, adipic acid, glutaric acid, or succinic acid in half-amidebond with AA0 or AA1 and in direct ester linkage to a hydroxyl group onthe surface of the nanocarriers); AA0 is present or absent, and whenpresent, AA0 is selected from the group consisting of L-arginine, anaturally occurring amino acid with an uncharged side chain (e.g.,sarcosine and glycine), and beta-alanine; AA1, AA2, AA3, AA4, AA5, AA6,AA7, AA8, AA9, and AA10 are present or absent, and when present areindividually selected from L-arginine or a naturally occurring aminoacid with an uncharged side chain; Y is an amide, a mono-substituted ordi-substituted alkyl amide (e.g., methylamide, ethylamide, anddimethylamide), or a PEG(4-12) amide; with the proviso that: thepeptides have a net positive charge and zeta potential between about +2to about +9, +10, +11, +12, +13, +14, +15, +16, +17, +18, +19, or +20mV; the peptides comprise at least 2 amino acids and no more than 11amino acids; and the amino acid sequence of the peptides includes atleast 2 L-Arginine residues, no more than 4 L-Arginine residues, and noother charged amino acids other than L-Arginine residues.

In some embodiments, the nanocarriers may be conjugated to peptideshaving a formula: X-peptide-Y, wherein: X is amino-PEG(4-12)-CO-, and Yis a mono-substituted or di-substituted alkyl amide (e.g., methylamide,ethylamide, and dimethylamide), or Y is a PEG(4-12) amide. Exemplarypeptides may include, but are not limited to:NH₂-PEG(4-12)-CO-Val-Ile-Thr-Arg-Ile-Arg-NH₂ (SEQ ID NO: 7);NH₂-PEG(4-12)-CO-Leu-Tyr-Arg-Val-Arg-NH₂ (SEQ ID NO:8); andNH₂-PEG(4-12)-CO-Arg-Arg-Ser-Ser-Arg-Arg-NH₂ (SEQ ID NO:9) and theN-terminal amino group is covalently linked to a hydroxyl on the surfaceof the nanocarriers through a carbamate linkage.

In some embodiments, the disclosed nanocarriers further may comprise adrug or pro-drug, for example conjugated to the nanocarriers or peptidesand/or adsorbed to the nanocarriers and/or peptides. In otherembodiments, the disclosed nanocarriers may comprise a drug or pro-drug,such as a lipophilic drug or pro-drug that is confined to in thelipophilic core of the nanocarriers. In even further embodiments, thedisclosed nanocarriers may comprise an antibody or an antigen-bindingfragment thereof (e.g. a therapeutic antibody such as an anti-VEGF-1antibody), for example, conjugated to the nanocarriers or peptidesand/or adsorbed to the nanocarriers and/or peptides. In even furtherembodiments, the disclosed nanocarriers may comprise nucleic acidadhered to the surface of the nanocarriers, optionally wherein thenucleic acid is RNA such as RNA used for RNA-interference therapyincluding siRNA. (See Thakur et al., “Strategies for ocular siRNAdelivery: Potential and limitations of non-viral nanocarriers,” J. Biol.Eng'g 2012 6:7; and Turchinovich et al., “Non-viral siRNA delivery intothe mouse retina in vivo,” BMC Ophthalmology 2010, 10:25, the content ofwhich is incorporate herein by reference in its entirety). SuitablesiRNA's may include, but are not limited to siRNA's that interfere withexpression of vascular endothelial growth factor receptor-1 (VEGF-1)such as Sirna-027. When the nanocarriers comprise nucleic acids, theanchoring peptides may include additional arginine residues (e.g., 3-4arginine residues rather than only 2 arginine residues) and/or theanchoring peptides may have a higher degree of loading in order tooffset the negative charge of the nucleic acids (i.e., such that the netpositive-charge of the nanocarriers is at least +2 mV).

The disclosed nanocarriers may be administered to a subject in needthereof, for example, in a method of treatment. As such, the disclosednanocarriers may be formulated as pharmaceutical compositions.

In some embodiments, the disclosed nanocarriers and/or pharmaceuticalcompositions comprising the disclosed nanocarriers are administered viainjection into a body cavity of a subject in need thereof. In someembodiments, the body cavity comprises a polyanions and has a netnegative charge. The disclosed nanocarriers may have a net positivecharge and may be immobilized in the body cavity having a net negativecharge via ionic interactions. In some embodiments, the disclosednanocarriers may be utilized in an ocular nanotherapy. Suitable bodycavities for administering the disclosed nanocarriers may include thevitreous humor, for example, where the disclosed nanocarriers areadministered to the vitreous humor of a subject in need thereof to treatan ocular disease or disorder (e.g., age-related macular degeneration,diabetic retinopathy, and/or glaucoma), or retinopathy of prematurity(ROP).

The disclosed nanocarriers and/or pharmaceutical compositions comprisingthe disclosed nanocarriers may be administered to a subject having aneovascular retinal disease, for example, where the nanocarrierscomprise an anti-angiogenic agent. In some embodiments, the neovascularretinal disease is macular degeneration.

The nanocarriers may be formulated based on the intended therapeutic useof the nanocarriers. For example, the nanocarriers may have an averageeffective diameter that is less than about 0.2 microns (e.g., when thecarriers are formulated for intravitreal administration). In someembodiments, the nanocarriers may have an average effective diameterthat ranges from 0.1 microns to 20 microns (e.g., when the carriers areformulated for intraperitoneal administration). Preferably, forintraocular applications, the carriers are optically transparent orsubstantially optically transparent (e.g., when the carriers are used inpreparing a prodrug for intravitreal administration). For example, atransparent or substantially transparent carriers may absorb and reflectless than about 10%, 9%, 8%, 7%, 6%, 5%, 4%, 3%, 2%, or 1% of incidentlight and/or may have a total transmittance of at least about 90%, 91%,92%, 93%, 94%, 95%, 96%, 97%, 98%, or 99% of incident light.

In some embodiments, the disclosed nanocarriers may be formulated fordelivering anti-angiogenic, VEGF neutralizing proteins (e.g., asmarketed under the trade names Lucentis™, Avastin™, and Eyelea™).Anti-angiogenic, VEGF neutralizing proteins are used to treat eyedisease by direct injection into the vitreous humor, the proteins allbind and neutralize the endogenous angiogenic protein, VEGF. Smallsynthetic molecule drugs (e.g., anti-inflammatory, anti-glaucoma,anti-infectious) can also be delivered by this route if their releasecan be sustained.

ILLUSTRATIVE EMBODIMENTS

The following embodiments are illustrative and should not be interpretedto limit the scope of the claimed subject matter.

Embodiment 1

Nanocarriers that are biodegradable or that can be excreted and have anet positive surface charge and zeta potential between about +2 to about+20 mV (e.g., +2, +3, +4, +5, +6, +7, +8, +9, +10, +11, +12, +13, +14,+15, +16, +17, +18, +19, or +20), wherein the net positive surfacecharge is provided by peptides that are covalently attached to thesurface of the nanocarriers.

Embodiment 2

The nanocarriers of embodiment 1, wherein the nanocarriers comprise apolymeric carbohydrate and are transparent, and preferably have adiameter that permits for filter sterilizing.

Embodiment 3

The nanocarriers of embodiment 1 or 2, wherein the nanocarriers comprisedextran which optionally is a condensed dextran hydrogel, chitosan,pullulan, or a dendrimer.

Embodiment 4

The nanocarriers of any of the foregoing embodiments, wherein thepeptides comprise C-terminal amide groups.

Embodiment 5

The nanocarriers of any of the foregoing embodiments, wherein thepeptides comprise at least 2 amino acids and no more than 11 aminoacids.

Embodiment 6

The nanocarriers of any of the foregoing embodiments, wherein the aminoacid sequence of the covalently attached peptides includes at least 2L-Arginine residues, no more than 4 L-Arginine residues, and no othercharged amino acids other than L-Arginine residues, and where the amountof covalently attached peptides produces a positive average zetapotential of the particles ranging from about +2 to about +20 mV.

Embodiment 7

The nanocarriers of any of the foregoing embodiments, wherein the aminoacid sequence of the attached peptides comprises an amino acid sequenceof a human protein that is secreted into the extracellular matrix orthat is found in vitreous humor, blood, urine, or saliva, or has anamino acid sequence that is at least 80% identical with thecorresponding sequence from the human protein that is secreted into theextracellular matrix or that is found in vitreous humor, blood, urine,or saliva.

Embodiment 8

The nanocarriers of any of the foregoing embodiments, wherein thepeptides include at their N-terminus a neutral amino acid residueselected from the group consisting of sarcosine, or beta-alanine.

Embodiment 9

The nanocarriers of any of the foregoing embodiments, wherein thepeptides are covalently attached to the nanocarriers via conjugationbetween hydroxyl groups on the surface of the nanocarriers and freeamino groups on the peptides.

Embodiment 10

The nanocarriers of any of the foregoing embodiments, wherein thepeptides are covalently attached to the surface of the nanocarriers viacarbamate conjugation between hydroxyl groups on the surface of thenanocarriers and an amino group appended to the peptide N-terminus,wherein the amino group is selected from the group consisting of a freealpha amino group on the peptides, a free beta, gamma, delta or epsilonamino acyl group on the peptides, as in epsilon aminocaproic acid, anamino-PEG(4-12) acyl amide of the peptide N-terminus, or apyrrolidyl-3-carboxylate amide or pyrrolidyl-3-amidosuccinyl amide of anamino-PEG(4-12) acyl amide of the peptide N-terminus.

Embodiment 11

The nanocarriers of any of the foregoing embodiments, wherein thepeptides are covalently attached to the surface of the nanocarriers viaamide conjugation between carboxyl groups on the surface of thenanocarriers and an amino group appended to the peptide N-terminus,wherein the amino group is selected from the group consisting of a freealpha amino group on the peptides, a free beta, gamma, delta or epsilonamino acyl group on the peptides, as in epsilon aminocaproic acid, anamino-PEG(4-12) acyl amide of the peptide N-terminus.

Embodiment 12

The nanocarriers of any of the foregoing embodiments, wherein thepeptides have a formula: B-Z-AA0-(AA1)_(n)-Y, where n is an integerbetween 1 and 10 where no less than two AA and no more than 4 AA areL-arginine, and all other AA are neutral (not lysine or glutaric acid oraspartic acid), wherein: B is present or absent, and when B is present,B is selected from the group consisting of amino-n-butoxy,amino-ethoxyethyloxy, amino-piperidyl (3, or 4)-oxy, amino-pyrrolidinyl(3)-oxy, amino-benzyl (3, or 4)-oxy, aminoethylamido-valeric acid(4)-oxy, amino-cyclohexyl (3, or 4)-oxy, and amino-cyclopentyl (3)-oxy;Z is absent or present, and when Z is present, Z is a dicarboxylic acid,including suberic, adipic, glutaric, dimethylglutaric, succinic in amidebond to AA0 or AA1, where the OH group of an above amino alcohol, B isbonded as an ester to the free dicarboxylic acid group in half-amidelinkage to or AA1; AA0 is present or absent, and when present, AA0 isselected from the group consisting of L-arginine, a naturally occurringamino acid with an uncharged side chain (e.g., sarcosine and glycine),and beta-alanine; AA1 is L-arginine or a naturally occurring amino acidwith an uncharged side chain; Y is an amide, a mono-substituted ordi-substituted alkyl amide (e.g., methylamide, ethylamide, anddimethylamide), or a PEG (4-12) amide; with the proviso that: thepeptides have a net positive charge and their multiple linkage tocarrier produces nanoparticles having zeta potential between about +2 toabout +20 mV; when peptide comprises from about 10% to about 50% of theconjugate mass.

Embodiment 13

The nanocarriers of embodiment 12 or 13, wherein B is anamino-PEG-carboxylic acid having between 4 and 16 ethylene glycol unitsin amide bond to AA0 or AA1, and Z is absent.

Embodiment 14

The nanocarriers of embodiment 14 wherein the conjugated modifiedpeptide is amino-PEG (4-12)-CO-Arg-Arg-Tyr-Arg-Leu-Y (SEQ ID NO:16),where Y is amide or ethylamide.

Embodiment 15

The nanocarriers of any of the foregoing embodiments, except embodiment3, in which the carrier contains surface carboxyl groups, as inhyaluronic acid or a carboxy terminal dendrimer wherein the linkingamino group is amide bonded to these carboxyl groups in sufficient yieldto give zeta potential from about +2 mV to about +20 mV in which somecarboxyl groups remain un-linked or where some of the carboxyl groupsare capped as neutral amides.

Embodiment 16

The nanocarriers of any of the foregoing embodiments in whichamino-PEG-OH or amino-PEG-OMe of molecular weight ranging from 200 to2,000 grams/mole are additionally appended to carriers through carbamateor amide bonds while comprising from about 10% to about 50% of theconjugate mass.

Embodiment 17

The nanocarriers of any of the foregoing embodiments formulated bymixing with clinical grade viscous hyaluronic acid (Healon) forimmobilization at sites of administration.

Embodiment 18

The nanocarriers of any of the foregoing embodiments, wherein Y is anamide, a mono-substituted or di-substituted alkyl amide (e.g.,methylamide, ethylamide, and dimethylamide), or a PEG(4-12) amide or a3-pyrrolidyl-3-carboxylate amide or pyrrolidyl-3-amidosuccinyl amide ofan amino-PEG(4-12) acyl amide of the peptide N-terminus; with theproviso that: the peptides have a net positive charge and their multiplelinkage to carrier produces nanoparticles having zeta potential betweenabout +2 to about +20 mV; when peptide comprises from 10-50% of theconjugate mass; the peptides comprise at least 2 amino acids and no morethan 11 amino acids; and the amino acid sequence of the peptidesincludes at least 2 L-Arginine residues, no more than 4 L-Arginineresidues, and no other charged amino acids other than L-Arginineresidues.

Embodiment 19

The nanocarriers of any of the foregoing embodiments, wherein Z is adicarboxylic acid selected from the group consisting of adipic acid,glutaric acid, and succinic acid in half-amide bond with AA0 or AA1 andin direct ester linkage to a hydroxyl group on the surface of thenanocarriers.

Embodiment 20

The nanocarriers of any of the foregoing embodiments further comprisinga pro-drug conjugated to the carrier.

Embodiment 21

The nanocarriers of any of the foregoing embodiments further comprisinga lipophilic drug loaded in the core of the nanocarriers.

Embodiment 22

The nanocarriers of any of the foregoing embodiments further comprisingantibodies or antigen binding fragments thereof (e.g., anti-VEGF-1antibodies) conjugated to the peptides.

Embodiment 23

The nanocarriers of an of the foregoing embodiments further comprisingnucleic acid adhered to the surface of the nanocarriers, optionallywherein the nucleic acid is RNA (e.g., siRNA such as siRNA that inhibitsexpression of VEGF-1).

Embodiment 24

The nanocarriers of any of the foregoing embodiments, wherein the aminoacid sequence of the peptides comprises an amino acid sequence of ahuman protein that is secreted into the extracellular matrix or that isfound in vitreous humor, blood, urine, or saliva.

Embodiment 25

The nanocarriers of any of the foregoing embodiments, wherein thecarrier-bonded peptides have a formula: X-peptide-Y, wherein: (1) X is adi-carboxylic acid of 4-10 carbons in length in half-amide bond with theN-terminus of the peptide, (2) X is succinic acid, glutaric acid, oradipic acid in half-amide bond to sarcosine which is in turn amidebonded to the N-terminus of the peptide, (3) X is succinic acid,glutaric acid, adipic acid, or suberic acid directly amide bonded to theN-terminus of the peptide when the peptide has an N-terminal proline, or(4) X is a dicarboxylated PEG (1-6 ethylene glycol units) half amidebonded to the peptide N-terminus and half amide bonded to the exocyclicamino group of 3-aminopyrrolidine; and (1) Y is an amide, (2) Y is amono-substituted or di-substituted alkyl amide (e.g., methylamide,ethylamide, and dimethylamide), or (3) Y is a PEG(4-12) amide.

Embodiment 26

The nanocarriers of any of the foregoing embodiments, wherein thepeptides are selected from the group consisting of:NH₂-PEG(8-12)-CO-Val-Ile-Thr-Arg-Ile-Arg-NH₂ (SEQ ID NO:7);NH₂-PEG(8-12)-CO-Leu-Tyr-Arg-Val-Arg-NH₂(SEQ ID NO:8);NH₂-PEG(8-12)-CO-Arg-Arg-Ser-Ser-Arg-Arg-NH2 (SEQ ID: 9); and theN-terminal amino group is covalently linked to a hydroxyl on the surfaceof the particles through an amide linkage or a carbamate linkage.

Embodiment 27

The nanocarriers of any of the foregoing claims, wherein the peptidesare selected from the group consisting of:3-pyrrolidine-CONH-PEG(8)-CO-Tyr-Arg-Val-Arg-Ser-NH₂ (SEQ ID NO:4); and3-pyrrolidine-CONH-PEG(8)-CO-Arg-Arg-Tyr-Arg-Leu-NH₂ (SEQ NO ID NO:5).

Embodiment 28

The nanocarriers of embodiment 12, wherein the appended esterifieddicarboxypeptide [B-Z-AA0-(AA1)n-Y] comprising from about 10% to about50% of the total nanocarriers mass is pyrrolidinyl(3)-oxy-adipic-Sar-Tyr-Asn-Leu-Tyr-Arg-Val-Arg-Ser-amide (SEQ ID NO:6).

Embodiment 29

Nannocarriers comprising the properties of embodiment 13 and ofembodiment 17 in which both an ester-linked bioactive peptide (eg: SEQID NO:6) and a 3Arg or 4Arg anchoring peptide (eg: SEQ ID NO:5 or SEQ IDNO:9) stably attached as carbamates are simultaneously conjugated to thesame CDEX particle, where bioactive peptide and anchor peptide eachcontribute from about 20% to about 40% of the conjugate mass, to enablesimultaneous prolonged intravitreal residence and continuous drugrelease.

Embodiment 30

A pharmaceutical composition comprising the nanocarriers of claim 1 anda suitable pharmaceutical carrier, which may include, but is not limitedto mixtures of cationic nanocarriers with natural poly-anions such ashyaluronic acid or heparins to immobilize and enhance the safety of thenanocarriers.

Embodiments 31

A method comprising administering the nanocarriers of any of theforegoing embodiments of a pharmaceutical compositing comprising thenanocarriers of any of the foregoing embodiments to a subject in needthereof.

Embodiment 32

The method of embodiment 31, wherein the nanocarriers are administeredvia injection into a body cavity comprising polyanions.

Embodiment 33

The method of embodiment 31, wherein the subject has an eye disease andthe cavity comprises the vitreous humor.

Embodiment 34

The method of any of embodiments 31-33, wherein the eye disease is aneovascular retinal disease.

Embodiment 35

The method of embodiment 32, wherein the neovascular retinal disease ismacular degeneration.

Embodiment 36

The method of embodiment 33, wherein the eye disease or disorder isdiabetic retinopathy.

Embodiment 36

The method of embodiment 31, wherein the body cavity is selected fromthe group consisting of the vitreous humor, the intraperitoneal cavity,and the intracranial cavity.

Embodiment 37

Modified peptides having a sequence selected from:4-aminocyclohexyl-O-adipoyl-Sar-Tyr-Asn-Leu-Tyr-Arg-Val-Arg-Ser-NH₂ (SEQID NO:6); or3-pyrrolidyl-O-adipoyl-Sar-Tyr-Asn-Leu-Tyr-Arg-Val-Arg-Ser-NH₂ (SEQ IDNO:6); or4-aminocyclohexyl-O-adipoyl-NH-PEG(4,8)-CO-Arg-Arg-Tyr-Arg-Leu-amide(SEQ ID NO:5); or3-pyrrolidyl-O-adipoyl-NH-PEG(4,8)-CO-Arg-Arg-Tyr-Arg-Leu-amide (SEQ IDNO:5) and their carbamate conjugates with condensed dextran70, havingzeta potential from +2 to +20 mV where peptide comprises 10-60% of thetotal conjugate mass or a 3-pyrrolidyl-3-carboxylate amide orpyrrolidyl-3-amidosuccinyl amide of an amino-PEG(4-12) acyl amide of thepeptide N-terminus.

EXAMPLES

The following Examples are illustrative and are not intended to limitthe scope of the claimed subject matter.

Example 1—Overview of Nanocarrier Technology

Here, we disclose a new approach to the anchoring of carriernanoparticles within certain body spaces for local, continuous drugdelivery, with particular emphasis on prolonged availability of drugsinjected into the vitreous humor of the eye. Previously, slow deliveryin the eye has relied on slowly diffusing large particles in the viscousgel environment or both smaller and larger ones with positive charges tobetter adhere to highly negatively charged polymers found in thevitreous. These types of carrier can be toxic to sensitive eyecomponents, and can be hard to control kinetically. Arginine has beenshown to be a safer source of (+)charge but has not previously beenattached as described here, where its loss is well-controlled. We relyon small carriers (<200 nm diameter) with positive charges on theirsurface, where this charge is derived from small arginine-containingpeptides with natural human amino acid sequences. The (+)charge perpeptide is low, but many of these on a carrier surface can give strongadherence to polyanions in the eye. Uniquely here, the peptides areattached to the carriers via bridges which break down spontaneously in afirst order process with half-lives of 1-4 weeks under physiologicaltemperature and pH. Thus, over time the surface charge is slowly lostuntil the carriers no longer adhere and then readily leave the eye.Drugs within or attached to the carriers will have their own releaserate which can be tuned to closely match the carrier particle release.Our preferred carriers are small enough to be sterile-filtered whenfully loaded with peptides and drug.

The details of this invention include: description of exemplary peptidesand the human proteins from which they are derived, appended groupsincluded for linkage, with description of how these are synthesized andtheir breakdown rate evaluated, and examples of carriers, theirproperties, and how the peptides are attached to them.

In order to provide a net positive charge, be non-immunogenic, and toavoid side-reactions the peptides to be linked to carriers as esterscontain between 2 and 11 naturally occurring L-amino acids in theirnormal sequence in human proteins of which 2 or 3, or 4 are L-arginine(Arg, R) residues. None are lysine, or Glu, or Asp and free carboxyltermini are preferably capped as amides. The N-terminal carrier-linkingamine may also be derived from amino-PEG(n)-COOH, where n is an integerfrom 4-12, bonded to the peptide at its amino terminus. Alternatively,the peptides may have appended at their N-terminus an amide bondeddi-carboxylic acid of 4-8 carbons in length for ester formation to aminoalcohols, B, from which amino groups can form bonds to carriers. TheN-terminal amino acid may be an added sarcosine (Sar, N-methylglycine)or may be L-proline from the parent protein sequence when the peptide isN-terminally capped with a di-carboxylate such as succinate or glutarateor adipate or suberate. The N-terminal amino acid may be any naturallyoccurring L-amino acid when the di-carboxylic acid is adipic acid or alonger chain half-amide.

Peptide Examples

A heptamer peptide of +2 net charge within P18 of the matrix protein,PEDF is: Ac-Leu-Tyr-Arg-Val-Arg-Ser-Ser-amide (SEQ ID NO:10). This has anet charge of +1 when the N-terminus is capped by a dicarboxylic acid,as in: adipoyl-Leu-Tyr-Arg-Val-Arg-Ser-Ser-amide (SEQ ID NO:10), whichthen increases to +2 in a half ester of a di-carboxylic acid such asadipic acid as in R-O-adipoyl-Leu-Tyr-Arg-Val-Arg-Ser-Ser-amide (SEQ IDNO:10) or in an amido ester which may be bridged stably to a carrierthrough an amide bond to an amino-alcohol ester as in:Carrier-CO-amido-butyloxyadipoyl-Leu-Tyr-Arg-Val-Arg-Ser-Ser-amide. Itmay be delivered to carrier with an amino-PEG cap as inamino-PEG(n)-CO-Leu-Tyr-Arg-Val-Arg-Ser-Ser-amide. The latter peptidehas net charge pf +3, which then becomes +2 upon carbamate attachment tocarrier OH groups. Succinic, glutaric, adipic and suberic acids can alsobe used as metastable ester bridged linkers when an N-methyl amino acid(e.g., Sarcosine, Sar) is appended to the peptide N-terminus, as in:Carrier-CO-amido-butyloxyadipoyl-Sar-Leu-Tyr-Arg-Val-Arg-Ser-Ser-amide.

Another series of human peptide sequences are shown, derived from humanthrombospondin-1 (TSP-1) where a normal human sequence therein is:Gly-Asp-Gly-Val-Ile-Thr-Arg-Ile-Arg-Leu. Within this sequence thesmaller Ac-Gly-Val-Ile-Thr-Arg-Ile-Arg-amide (SEQ ID NO:1) has +2charge, and can be linked via an extended amino-PEG linker, or as anadipic ester as in: amino-R-O-adipoyl-Gly-Val-Ile-Thr-Arg-Ile-Arg-amide(SEQ ID NO:1), with alternative links analogous to those described abovefor the PEDF series, as in:RO-adipoyl-Sar-Gly-Val-Ile-Thr-Arg-Ile-Arg-amide (SEQ ID NO:11).Amino-PEG-peptides comprising just the last 4-5 amino acids of the abovesequence are also appropriate as +2 charge anchor peptides.

The same approach can be taken with sequence from human fibrinopeptideB-beta, which circulates in blood and is found in human urine, thusunlikely to be immunogenic. The peptide contains the sequence:Ser-Gly-Gly-Gly-Tyr-Arg-Ala-Arg-Pro-Ala (SEQ ID NO:12). Appropriatelinkable derivatives as above, from the fibrinopeptide may include:R-O-adipoyl-Gly-Gly-Tyr-Arg-Ala-Arg-Pro-amide (SEQ ID NO:13); orR-O-adipoyl-Sar-Gly-Tyr-Arg-Ala-Arg-Pro-amide (SEQ ID NO:14).Amino-PEG-capped peptides comprising the truncated distalTyr-Arg-Ala-Arg-Pro-amide from the above sequence are also appropriateas +2 charge anchor peptides.

For anchoring peptides with +3 charge that can be conjugated to dextrancarriers, we select the natural sequence pentapeptide:Arg-Arg-Tyr-Arg-Leu (SEQ ID NO:5) from within the sequence: . . .Phe-His-Arg-Arg-Tyr-Arg-Leu-Pro . . . (SEQ ID NO:15) conserved inchaperone proteins Hsp20 and alpha-A crystallin (aa118-124), which arefound in the circulation and in the eye [AR Clark et al. Crystalstructure of R120G disease mutant . . . J Mol Biol 408:118 (2011)]. Thusamino-PEG (4-12)-CO-Arg-Tyr-Arg-Arg-Leu-amide (SEQ ID NO:5) will displaynet charge of +3 for every peptide appended to a carrier OH groupthrough amino-terminal linkage.

Ester linkable peptides from all the human sequences described abovehave 6-7 amino acids in exact human sequence. However, as many as 10 insequence are acceptable, with up to one additional linker amino acid atthe N-terminus and/or a single di-carboxylic acid appended at theN-terminus.

Other positively charged small peptides found in urine include fragmentsof human protamine, which is very rich in Arg residues, thus can enhance(+)charge, even in small peptides. One such naturally occurringprotamine fragment is Pro-Arg-Arg-Arg-Arg-Ser-Ser-Ser-Arg-Pro (SEQ IDNO:16). Based on this sequence, smaller portions therein can be used asin: R-O-adipoyl-Arg-Arg-Ser-Ser-Ser-Arg-Pro-amide (SEQ ID NO:17), or a4Arg version as in R-O-adipoyl-Pro-Arg-Arg-Arg-Arg-Ser-amide (SEQ IDNO:18). Each of the above examples provides +3 net charge on theester-linked peptide. Also, with proline at the N-terminus adipate,glutarate and succinate are also acceptable linking moieties to thecarrier. Thus, amino-PEG(4-12)-CO-Pro-Arg-Arg-Arg-Arg-Ser-amide (SEQ IDNO:18) is an appropriate +4 peptide to be linked, and may also beembodied in N-terminal bridged ize with displacement of the ester, asin: amino-R-O-glutaryl-Pro-Arg-Arg-Arg-Arg-Ser-Ser-amide (SEQ ID NO:18),also giving a +4 net charge, where Pro is from the normal sequence, arecontemplated herein, and is less likely than primary amino acid tocyclize through attack on the ester bridge.

The carriers described here include (but are not limited to) dendrimersand polymeric carbohydrate gels. OH-terminal carriers gain the totalcharge of carbamate appended amino-acyl or amino-PEG peptides, whileexcess peptides are needed for COOH-terminal carriers to maintaincationic charge. Peptides, each having +4 charge when linked as amidesto just 30% of a 64 carboxyl dendrimer, will add +76 charge perdendrimer, with only 45 COOH then remaining, these have +31 net charge.With 40% of the available sites linked this way, the net charge will be+64, thus will be more tightly anchored via multiple weak forces tovitreal hyaluronic acid.

Synthesis of the ester-bridged versions can be achieved by attaching ashort N-BOC-amino-alcohol (e.g., 4-BOC-amino-1-butanol or4-N-BOC-amino-cyclohexanol, or N-BOC-3-pyrrolidinol) in ester linkagewith the free carboxyl group of adipic acid, after reaction with adipoylchloride. The BOC-amido-alkyl half-ester of adipic acid is thenN-terminally added to the peptide by well-established solid state amidecoupling techniques to an appropriate solid state peptide at its freesarcosine N-terminus, after which standard acidic de-blocking andpeptide release then gives the salt ofamino-alkyloxy-ester-Sar-AA1-AA2-AA_(n) . . . -amide (where n=1-10) withan amide capped C-terminus, ideally to maintain positive charge, andwhere 1, 2, 3 or 4 of the aa residues are Arginine, flanked andconnected to each other by normal human sequence identical to that foundin their parent protein. The free N-terminal amine group is then amidebonded to a carrier (e.g., a carboxy dendrimer, hyaluronic acid, and thelike) by common methods of acyl activation, so that multiple amidoester-linked (+ or ++ charged) peptides are present on the carriersurface. Typically for a water-soluble carrier, coupling will utilizewater soluble carbodiimide and sulfo-NHS. Activated but unreactedcarboxyl groups of the carrier can then be capped and neutralized withother uncharged amides (e.g. by reaction with methoxy-PEG-amine,beta-alanine amide, etc.) to increase overall positive charge (positivezeta potential). For carbamate linkage to an OH terminal carrier, the OHgroups are first activated by reaction in DMSO, with eithercarbonyldiimidazole (CDI) or with p-nitrophenylchloroformate (pNP-Cl).The activated carriers are then linked to peptide by reaction of freenon-alpha amino groups of amino-alkyl-peptide, amino-PEG-peptide oramino-alkoxy ester peptides. Any remaining activating groups are thendischarged by reaction with excess ethanolamine or PEG (4-12)-amine. ApNP-Cl advantage is colorimetric estimation of appended activatinggroups, and detection of complete removal.

Amino Alcohols for Ester Coupling

Our use of several varied amino-alkoxy esters gives a range ofspontaneous hydrolytic rates of ester breakdown at physiologicaltemperature and pH which can be predicted from kinetic analysis of modelesters. Inclusion of an ester bridge insures gradual loss of theanchoring charge, and can be adjusted to control the duration ofintravitreal residence through continuous decline in zeta potential withtime.

An important aspect of the peptide-loaded carriers is that they have apositive zeta-potential, i.e. a net positive charge concentrated ontheir surface in order to immobilize them at their site of injectionthrough multiple weak ionic interactions with polymeric anionic groupsin the vitreous or on mucosal surfaces. This derives from the fact thateach attached peptide, when esterified has a net charge of at least +1,and is especially critical for use in the eye, which contains highconcentrations of the viscous poly-anionic hyaluronic acid (HA). Thus anideal particle to be used for intravitreal injection will be less than200 nm in diameter when fully charged with peptide and drug, a size thatdoes not impede diffusion out of the eye when neutral or negativelycharged, but in our system will have net charge of +40 to +240 per100-150 kDa particle, for long-term anchoring. Ideally, >50% ofparticles injected in 0.05 ml should be contained within a 0.25-0.50 mlspherical volume at the injection site, if measured 7 dayspost-injection, because of adherence to HA in the vitreous humor. Thiscan be established by light loading (1-3%) with rhodamine, cyanine7 orother fluorophores, attached to the peptide-loaded carriers, theninjected (1-50 ul) into rabbit vitreous or rodent eyes, as in FIGS. 8and 9.

Measuring Peptide Release Half-Life.

For use in the eye, the ideal half-life of ester cleavage by simplehydrolysis at 37° C. and pH 7.4 should be 20-60 days. Approximately0.1-1 mg of peptide attached to 0.1-1 mg of the carrier would bedelivered in the eye in a maximum 50 μl injection volume. Our carrierswill not pass through a 30 kDa MWCO centrifugal spin filter. Thus BCAprotein analysis of increasing peptide, with time in filtrate after 30kDa filtration of a loaded carrier sample in buffer estimates thehalf-life for peptide release in buffer. For confirmation in actualvitreous humor (e.g., rabbit) at time points post injection LC-MSestimation of the peptide in vitreous extract follows precipitation ofexcess HA after adding 3 volumes of ethanol. The half-life of residenceof peptide-conjugated carriers in the vitreous of test animals such asrabbits was measured by tagging the carriers with long wavelength dyes(eg; Cyanine7) and measuring residual eye fluorescence over time by invivo imaging system (IVIS), with excitation at 745 nm, emission 800 nm(FIGS. 8 and 9). Free intravitreal peptide is assayed aftercentrifugation via 30 kDa MWCO spin filter.

Drugs and Pro-Drugs for Delivery.

Hydrophobic small molecule drugs may be contained within hydrophobiccores of condensed gel particles (e.g., cholesteryl hyaluronic acid orcholesteryl dextran) or may be attached through labile (e.g., ester)bonds to unreacted surface groups. Antibody attachment (e.g., Avastin)will be through a bi-functional linker, containing an ester bridge, forexample (amino-alkoxy ester-peptide-maleimide), where the proximal endis-bonded to the carrier and the distal maleimide is bonded to acysteine sulfhydryl group obtained by TCEP or DTT reduction of one ormore antibody disulfide groups or to VEGF-binding proteins that havebeen genetically modified to include a single free cysteine residue.Ester hydrolysis then releases the attached protein drug.

Example 2—Generation of Dextran Nano-Gels

4 g of dextran (M.W. 70,000, unit M.W. 190) was dried by co-evaporationwith anhydrous pyridine in vacuo and activated by reaction with 93 mg1,1′-carbonyldiimidazole (CDI) in 100 mL of anhydrous dimethyl sulfoxide(DMSO) at 25° C. under stirring for 4 h. Cholesteryl-amine wassynthesized by modification of cholesteryl chloroformate with a 3-foldexcess of 2,2′-(ethylenedioxy) bis (ethylamine) and purified by columnchromatography on silicagel using a stepwise gradient of methanol indichloromethane. 342 mg of cholesteryl-amine dissolved in 10 mL of DMSOwas added to the activated dextran, and reaction mixture was stirred for24 h at 25° C. The product (CDEX) was purified by dialysis insemi-permeable membrane tubes (MWCO 12-14,000) against water at 4° C.under stirring overnight, sonicated for 15 min and, then, freeze-dried.Total yield was 86%.

Particle size, Micro/nanogel nm PDI SD Yield, % Treatment CDEX 55 (100%)0.27 4 86 Sonication

Example—3 Activation of Nano-Gels

Nano-gel particles can be modified before charging with amino-peptidesor peptide intermediates using chemical activation of hydroxyl groups ondextran/dextrin with 1,1′-carbonyldiimidazole. 210 mg CDEX was dried byco-evaporation with anhydrous pyridine and mixed with 36 mg1,1′-carbonyldiimidazole (CDI) in 10 mL anhydrous DMSO. Reaction mixturewas stirred for 4 h at 40° C. The activated CDEX was purified bydialysis in semi-permeable membrane tubes (MWCO 12-14,000) against waterat 4° C. under stirring overnight and, then, lyophilized. Total yield ofthe imidazole-activated CDEX was 69%. Proton NMR showed that 58imidazole groups was attached to the polymer molecule (0.7 mmolimidazole moieties per 1 g).

45 nEq of the complex CDEX were dissolved in a solution of DMSO:pyridine1:1 (v:v) then, 63 μEq of pNP-Cl were added to the solution and 3 mM ofDMAP. The reaction was incubated at −40° C. overnight. An aliquot wastaken from the reaction and mixed with ethyl acetate. Aftercentrifugation (14,000 g, 1 minute, room temperature), the pellet wasdissolved in D2O and proton NMR showed the presence of the CDEX-pNP.After weighing and dilution into a specified volume of NaOH (0.1 M), thesample was evaluated by UV (A=400 nm, pH:8 Cε: 18.234 M-1 cm-1) fortotal pNP content. UV spectrophotometry showed 108 pNP per particle ofCDEX.

Example 4—Conjugation of Amino-PEG-Peptides

Amino-PEG(12)-peptides containing 1, 3 or 4 arginine residues (API, M.W.1,200; AP3, M.W. 1,375, and AP4, M.W. 1,550) have been conjugated withCDI-activated CDEX nanogel and investigated in biological systems.Urethane bonds (carbamates) formed in this reaction are stable in mostbiological environments.

Imidazole-activated CDEX (20 mg) was dissolved in 0.5 mL water, and pHwas adjusted to 8 with sodium bicarbonate solution. 9.6 mg of a 3-Argpeptide AP3, amino-PEG(12)-CO-Arg-Arg-Ser-Arg-amide (SEQ ID NO:19), wasdissolved in 0.2 mL DMF and mixed with the CDEX solution. Reaction wascontinued overnight at 25° C. and, then, quenched with 5 μL ethanolamineovernight at 4° C. Carrier-peptide conjugates were purified by dialysisin semi-permeable membrane tubes (MWCO 12-14,000) against water at 4° C.under stirring overnight and, then, freeze-dried. The reaction wasrepeated similarly for 9.6 mg AP3, and 10.9 mg AP4.

Carbamate linkage of amino-PEG peptide with 3 Arg residues

Size, nm Z-potential, Sample Peptide, % (SD) PDI mV Yield, % CDEX-AP3 31124 ± 1.4 0.167 4.58 58

Alternative Carbamate Attachment of Arg-Peptide with Long Wavelength Dye

An especially favored small 3-Arginine peptide is RRYRL (SEQ ID NO:5),because this sequence occurs naturally in two eye proteins, alpha Acrystallin and Hsp20. Its conjugate to CDEX can be followed by an InVivo Imaging System (IVIS) if the conjugate is tagged with cyanine aminedye. A UV-VIS spectrum of the 3Arg peptide (SEQ ID NO:5) and the Cy7 dyeconjugated to the nanocarrier (Cy7-CDEX70-3pyrrol-PEG8-RRYRL-NH2) wasprepared. The λ_(max) tyrosine of the peptide was 275 nm with anestimated 67 peptides per particle of CDEX. The λ_(max) of Cy7 was 750nm with an estimated 0.5 dye molecules per particle of CDEX.

CDEX Conjugation with Amino-PEG(4)-Arg-Arg-Tyr-Arg-Leu-amide (SEQ IDNO:5).

5 mg (0.067 moles containing 25 moles free glycosyl units) of thecholesterol-dextran complex (CDEX) synthesized from dextran-70 kD wasdissolved in 200 μl of anhydrous DMSO. Then 10 μl of dry pyridine wasadded to the solution, followed by 1.8 mg (8.67 moles) of 4-nitrophenylchloroformate.

After 5 minutes, 4 μl of 4-(dimethylamino)pyridine (DMAP) stock solutionat 150 μM in DMSO was added to achieve a final concentration of 3 mM.The reaction was incubated 1 hour at room temperature, after which wasadded 240 μg (0.33 μEq) of Cyanine7 amine (Cy7), stock solution at 20 mMin DMSO. The reaction was incubated during 1 hour at 50° C. Then, 29.2mg (26 moles) of the amino-PEG-peptide (TFA salt) was pre-dissolved in100 μl of anhydrous DMSO with 3 μl (34.7 μEq) of triethylamine (TEA).This solution is added to the reaction. The mixture (approx. 300 μl) wasreacted in a 2 ml sealed vial at 50° C. for 72h. After cooling to roomtemperature 26 μmoles of m-PEG₄-NH₂ was added to quench the reaction,for 1 hour at 37° C. The solution at RT was mixed with 1.0 ml of 0.1Mhydrochloric acid. It was then dialyzed twice against 2 liters of 0.001M HCl over 2 days at room temperature, using 12000 MWCO dialysis tubing.The dialyzed solution was sterile-filtered (0.2 μm), frozen andlyophilized.

The conjugated powder was dissolved in water at 0.2-2 mg/ml UV (λ=275nm) and VIS (λ=750 nm) spectrum obtained. Covalent peptide linkage wasestimated by UV spectrum, using a molar extinction coefficient of 1,100per peptide tyrosine residue at 275 nm after correction by subtractingthe UV spectrum of the same concentration of unreacted CDEX. The amountof Cy7 linked to the CDEX was established by Cy7 molar extinction of199,000 of dye at 750 nm. A sterile-filtered solution of CDEX conjugatehaving 21 peptides per CDEX monomer and 0.05 Cy7 per CDEX monomer wasthen tested in comparison to conjugate having only 14 peptides/CDEX, andsimilarly tagged with Cy 7 dye. (See FIG. 7.)

CDEX Conjugation with3-pyrrol-O-adipic-N-Sar-Tyr-Asn-Leu-Tyr-Arg-Val-Arg-Ser-amide (SEQ IDNO:6).

Synthesis of6-{[1-(tert-butoxycarbonyl)pyrrolidin-3-yl]oxy}-6-oxohexanoic acid

3 mEq of adipic chloride were dissolved in 10 ml of dichloromethane(DCM) at room temperature under stirring. On the other hand, 1 mEq ofthe amino-alcoxy compound was dissolved in DCM with 1 mEq oftriethylamine (TEA). This solution was added to the first one dropwise.After 30 minutes of reaction, the mixture was dried under vacuum and thecrude was dissolved in a solution of sodium bicarbonate 1 M. Thesolution was washed with ethyl acetate and both phases were mixed in aseparation funnel. The aqueous phase was extracted and the pH wasadjusted to 3-4 with 1M HCl. Then, the solution was extracted withether. The organic phase was dried under vacuum. Appearance:yellow-orange oil. The molecular weight of the compound was 315.36g/mol. The yield of the reaction was 46.6%.

¹H NMR (500 MHz, Chloroform-d) δ 4.96 (p, J=7.1 Hz, 1H), 4.10 (dd,J=9.5, 7.0 Hz, 1H), 3.78 (dt, J=9.5, 7.1 Hz, 1H), 3.52 (dt, J=9.5, 7.1Hz, 1H), 3.37 (dd, J=9.4, 7.1 Hz, 1H), 2.63 (td, J=12.5, 1.5 Hz, 1H),2.40-2.30 (m, 2H), 2.32-2.22 (m, 3H), 2.08-1.77 (m, 3H), 1.66-1.55 (m,1H), 1.47 (s, 9H).

Synthesis of the Ester Prodrug3-pyrrol-O-adipic-N-Sar-Tyr-Asn-Leu-Tyr-Arg-Val-Arg-Ser-amide (SEQ IDNO:5)

To HN-Sar-YNLYRVRS (SEQ ID NO:5) on Rink Amide 4-Methylbenzhydrylamine(MBHA) resin in DMF was added 1.5 mEq of Comp 1, 1.45 mEq(1-[Bwas(dimethylamino)methylene]-1H-1,2,3-triazolo [4,5-b] pyridinium3-oxid hexafluorophosphate) (HATU), and 6 mEq ofN,N-diisopropylethylamine (DIPEA). The reaction mixture was shaken on amechanical shaker overnight (16 h) at room temperature. The resultingpeptide was cleaved from the resin using a mixture of 95%trifluoroacetic acid (TFA), 2.5% water, and 2.5% triisopropylsilane for3 h. Crude peptide was precipitated from this solution using colddiethyl ether before purification by HPLC. Appearance: white powder. Themolecular weight of the compound was 1337.55 g/mol. The yield of thereaction was 26%. A mass spectrum analysis of the peptide was performedwhich exhibited a peak at 1336.8091 (m/z).

CDEX Conjugation with3-pyrrol-O-adipic-N-Sar-Tyr-Asn-Leu-Tyr-Arg-Val-Arg-Ser-amide (SEQ IDNO:6).

After the CDEX activation, the sample (mass: 2.3 mg) was dissolved inEtOAc and was centrifuged (14,000 g, 1 minute, room temperature). Thepellet was dissolved in DMSO (300 μl) and the mixture wasrotary-evaporated to remove trace solvent. Then, 6.75 μEq of the prodrugwere dissolved with 16.9 μEq of TEA (proportion 1:2.5) in anhydrous DMSO(200 μl). This mixture was added to the first one and the vial wassealed under anhydrous conditions in a nitrogen atmosphere. The reactionwas placed in an orbital shaker at 100 rpm, 45° C. over 3 days.

After 3 days, the reaction was stopped. To quench the active pNP, 13.5μEq of m-dPEG®₄-amine were added to the reaction and it reacts during 1hour at room temperature. After that, 0.01 M of HCl solution was addeddropwise getting the final pH=4. The mixture was dialyzed against 2liters of HCl 0.1 mM at 4° C. during 24 hours changing the bath every 4hours. MWCO: 50,000 Da. The solution was sterile-filtered andfreeze-dried. Results have showed in Table 1.

TABLE 1 Characterization of CDEX70-3pyrrol-adipic-N-Sar-Tyr-Asn-Leu-Tyr-Arg-Val-Arg-Ser-amide (SEQ ID NO: 5). Yield (%) 78 Size (nm) 178.3 ±9.42  Zeta potential (mV) 2.31 ± 0.38 Peptide/CDEX by BCA 30Peptide/CDEX by UV  57* Half-life (physiol. cond.) (days). 28 *Thepeptide quantification was taken to be that established by UV Tyrspectrum. UV (based on Tyr molar extinction of 1,100 at 276 nm). BCA isconsidered less accurate when peptide is appended to carrier, where freepeptide is used as BCA reference standard.

Example 5—Characterization of CDEX-Peptide Conjugates

Peptide content in carrier-peptide conjugates was measured using aPierce BCA Protein Assay based on the calibration curve obtained withthe corresponding free peptide. Peptide analysis was performed asfollows: 20 mg/mL stock solution of peptide in water was used to prepareserial 1/2 dilutions of standards. Then, BCA working reagent (WR) wasprepared by mixing 50 mL of BCA reagent A (50 mL) with 1 mL of BCAreagent B. 25 μL of each standard dilution and a carrier-peptideconjugate sample (3-5 mg/mL) were placed into 96-well plate intriplicates, then 200 μL of WR was added to each well, and the plate wasmixed thoroughly in shaker for 30 sec. Plate was covered and incubate at37° C. for 30 min, cooled at 25° C., and the absorbance was measured at562 nm using a plate reader. Peptide content (%) in the samples wascalculated based on the calibration curve of free peptide.

Sample characteristics (particle size, polydispersity andzeta-potential) were measured by a dynamic light scattering method usingMalvern Zeta Sizer Nano-S90 instrument according to the manufacturerrecommendations. Briefly, hydrodynamic diameter (d_(h)) andpolydispersity index (PDI) of nanogel/microgels were obtained for 1mg/mL aqueous solutions at 25° C. in triplicates after sonication for 30min and centrifugation at 12,000 rpm. Zeta-potential of the samples wasmeasured for the same solutions in standard 1 cm-cuvettesusingzeta-potential option in the company's software. Average of fivemeasurements±SD was registered.

Example 6—L-Arginine Peptide-Conjugated Nanocarriers for SustainedIntravitreal Drug Release

Reference is made to the article by Li et al., “Sustaining IntravitrealResidence With L-Arginine Peptide-Conjugated Nanocarriers,” Invest.Ophthalmol. Vis. Sci. 2017; 58:5142-5150, October 2017, the content ofwhich is incorporated herein by reference in its entirety.

Abstract

Neovascular retinal diseases affect millions of people worldwide, andresult in loss of vision and blindness if left untreated. Intravitrealinjection of angiogenic antagonist proteins is currently the standardand most efficient method for retinal drug delivery. However, repeatedinjections are required to maintain effective drug concentrations,imposing treatment burdens, pain and risk of complications on patients.Sustained release of therapeutics by injecting colloidal carriers is apromising approach to reduce injection frequency. However, the micronscale of carriers' dimensions required for slow diffusion canpotentially promote glaucoma and inflammation. Small, poly-cationicparticles can be immobilized in vitreous through multiple ionicinteractions with hyaluronic acid, resulting in slow diffusion, but suchparticles are generally toxic. Recently, particles containing L-Arginineas the only cationic source in their polymeric structure have beenreported with greatly improved biocompatibility. Here, we synthesizedand examined a novel type of biocompatible dextran-based nano carrier(<50 nm in diameter) conjugated stably with peptides containingL-Arginine for sustained release of therapeutic agents in the vitreous.We experimentally confirmed the poly-anion binding by competitionstudies with protamine in isolated rodent vitreous. We found that thediffusion rate of nano-carriers was inversely related to the values ofzeta potential ex vivo in freshly isolated rat vitreous and observedincreased intra-ocular half-lives in vivo. The longest clearance periodin vivo was over 240 days.-Histological examination demonstrated noadverse effects on ocular morphology and organization at 3 weeks to 36weeks. By combining the advantages of a small size and a long half-life,our novel peptide-conjugated carriers provide a safe and clinicallypractical means of sustained therapeutic release of agents againstposterior eye diseases.

Introduction

Retinal and posterior segment diseases affect nearly 10 million peoplein the United States [1]. Untreated, they result in loss of vision. Theeffective treatments largely rely on a safe intravitreal (IVT) drugdelivery. The unique anatomical and physiological barriers of the eyeblock outside drug molecules from entering the posterior segment, thus,leaving the delivery efficiencies of conventional topical orsystemic/oral drug administrations to be less than 5%. Currently,intravitreal injection is the most efficient method for posterior eyedrug delivery. This directly delivers active agents near the lesions,increasing the local drug concentration with low systemic exposure.Intravitreal injection is the primary method to treat endophthalmitis,sub-macular/vitreous hemorrhage, retinal vascular occlusion, advancedexudative age-related macular degeneration (AMD) and diabeticretinopathy. Acceptance of intravitreal injections has grown rapidlybecause of the injection of vascular endothelial growth factor (VEGF)inhibitors, which slow down the progress of neovascular retinaldiseases, such as AMD and diabetic retinopathy. In 2012, more than 2.3million injections were reported, and the number is estimated to benearly 6 million in 2016. Patients will endure a burden of frequentinjections over the long-lasting treatment period. Most therapeuticagents are typically eliminated from vitreous in a short time followingtheir administration. Consequently, repeated injections are needed tomaintain a therapeutically effective concentration in the posterior eye.For example, the half-life of Ranibizumab (a VEGF inhibitor fortreatment of advanced AMD) in human vitreous is approximately 9 days,requiring one administration per month. Frequent intravitreal injectionsraise the patients' discomfort, and cumulatively increases the risk ofpotential complications, such as vitreous hemorrhage, cataract andendophthalmitis [1,2]. Additionally, frequent outpatient visit is aburden on patients, who typically cannot drive, and significantlyincrease total treatment costs.

In recent years, there have been efforts to overcome the shortcomings ofmultiple injections by extending the time of therapeutic release afterdelivery. Use of the slow-released colloidal drug carrier is typical.The latter are normally nano/micro-spheres made of biodegradablematerials, with drug molecules embedded in their body or coated on theirsurface. After injection, the carriers remain in the vitreous over arelatively long time and slowly release the therapeutic molecules duringtheir breakdown to smaller fragments to enable complete clearance. Onecritical limitation of colloidal carriers is their relatively largesize. Colloidal carriers generally rely on large particle size (over 1μm) to slow the diffusion through the viscous vitreous. Large colloidalcarriers are not amenable to sterile filtration, and they or theirbreakdown products with a continuum of intermediate sizes may blockvision and/or may block or interact with the trabecular drainage. 200-nmpolystyrene particles coated with cationic amine groups showed diffusionrates of 1000-fold slower than their neutral or anionic counterparts inbovine vitreous [3]. Use of such cationic carriers, however, was notclinically practical since the particles are conjugated with multipleamino groups, which, along with most other cationic groups, are toxic,especially when the particles are of a size that can be engulfed bycells.

Recently, it has been reported that when the positive charge is entirelyderived from L-Arginine (L-Arg), small cationic particles could be atleast two orders of magnitude less toxic to cells. Zern et al [4]described a systematic comparison of cytotoxicity among cationicnanoparticles with varied sources of positive charges, including L-Argand D-Arg. While all the particles are capable of forming complexes withpolyanions, the L-Arg-based carriers were at least 200-fold less toxicthan the non-arginine based cationic carriers and at least 10-fold lesstoxic than D-Arg carriers. L-Arg could be a practical and safe cationicgroup for clinically applicable nanoparticle carriers in vitreous humor.

Thus, we designed and fabricated a novel type of L-Arg based cationicnanoparticles, aiming to establish non-toxic, biocompatible therapeuticcarriers for ocular drug delivery. Our nanoparticles were less than 50nm in diameter, made from the neutral polysaccharide, dextran, withL-Arg containing peptides linked on the surface to provide non-toxicpositive charges for vitreous anchoring. We experimentally confirmedionic binding as the mechanism of particle trapping in a chargedependent manner, measured particle diffusion rate ex vivo and monitoredthe half-life in vivo in rat vitreous, and their relations with surfacecharge of the carriers (ζ-potential). We further evaluated the adverseeffects of fabricated nanoparticles on ocular integrity by histologicalexamination.

Material and Methods

1. Nanoparticle Carrier Design

An illustrated conception of the nanoparticle structure is shown in FIG.1(a). We chose condensed clusters of cholesteryl dextran (CDEX, 3-5 mole%, hydrophobic domain is presumed roughly at the particle center) ascore material of the nanoparticles. Dextran is a biocompatible compound[5] widely used in FDA approved plasma expanders and ocular products. Itcan form compact spherical nanoparticle carriers with a large variety ofmolecular weight. We chose the CDEX nanoparticles smaller than the poresize of trabecular meshwork and vitreous collagen fiber meshwork (lessthan 50 nm).

Cationic peptides providing anchorage were covalently attached to theCDEX particle surface by carbamate attachment through activation of OHgroups of sugar units in CDEX. The peptides were designed to containnaturally occurring amino acid sequences from proteins commonly found inplasma or extracellular matrix in order to minimize toxicity andimmunogenicity. First, four distinct peptides, containing 4-8 aminoacids providing positive charges from 1 to 4 L-Arg groups, were boundcovalently to the surface. (As described later, the 4 L-Arg peptideconjugate, with zeta potential of 9-10 mV, was highly immobilized invitreous humor, and its diffusion was not further studied.) We chosepeptides of approximately 50 to 75 A in total length, with 20 to 30 A ofcationic groups linked through approximately 30 to 45 A spacers ofN-terminal amino-PEG groups (8.12 EG units). The L-Arg groups would beat the distances of 35 to 60 A extended from the particle surface. Weestimated 15 to 30 peptides were conjugated to one CDEX particle(Unconjugated particle is 77 kD). This enables Arginine cations to movefreely at the particle surface to access and pair with anionic units ofHA and similar polymers. Rhodamine B chromophore was also covalentlyconjugated to the particle surface with a density of about onechromophore per particle as a tag for fluorescence imaging.

The proposed mechanism of the long-lasting nanoparticles in vitreous isshown in FIG. 1(b). Vitreous humor is a transparent gel containing 99%water, with highly cross-linked collagen fiber-hyaluronic acid networkto maintain the shape. Hyaluronic acid molecules are anionic and in arandom coil structure. HA fills the space between collagen fibers toprevent aggregation. Our nanoparticles are immobilized by the ionicbinding between peptides anchored on the particle surface (circles) andhyaluronic acid molecules (strands).

2. Nanoparticle Carrier Synthesis

BOC-amino-PEG(n)-carboxylic acids were obtained from Quanta BioDesign,Plain City, Ohio. Rhodamine (Rh) isocyanate was from Thermo Fisher.Ethanolamine, carbonyldiimidazole (CDI), cholesteryl chloroformate,mono-BOC-ethylenediamine, and dextran (Leuconostoc, 70 kD) were fromSigma Aldrich. Amino-rhodamine (a-Rh) was formed by reaction ofRh-isocyanate with excess mono-BOC-ethylenediamine. It was purified bysilica gel chromatography (CH₂Cl₂:MeOH, 4:1). BOC was removed with 30%Trifluoroacetic acid (TFA) in CH₂Cl₂.

CDEX gel was formed by adding 0.3 g cholesterol chloroformate and oneequivalent of triethylamine in 8 mL dichloromethane into 45 mL anhydrousstirred DMSO containing 3.0 g dry Dextran, reacting at 40° C. for 3hours. After quenching with 45 mL water, the mixture was dialyzedexhaustively against water, and freeze dried. The crude product wasre-dissolved in 50 mL water and sonicated (Branson bath) for 2 hours.The solution was then filtered through 0.8 μm, 0.45 μm and 0.2 μmsyringe filters consecutively to remove suspended material before finallyophilization.

In the synthesis of the CDEX, cholesteryl groups covalently attach to3-5% of the sugar monomers of dextran, in which the attached cholesterolforms a core, thereby condenses the polymer into a compact sphere [6].Small lipophilic compounds can then be carried in the core while theentire carrier remains water-soluble, presenting a surface ofhydrophilic sugars. Those surface hydroxyl groups can be conjugated tomultiply hydrophilic drugs or targeting agents such as proteins orpeptides. Here we utilize such conjugation to cationic peptides toenhance residence time of nanoparticles in the vitreous humor.

Four peptides for conjugation were synthesized by solid state methodswith FMOC coupling methods on RINK amide resin, with final coupling toBOC-PEG-acid, and resin release and de-blocking with TFA. Each Peptidecontains an amino-PEG(n)CO-cap at its n-terminus, where n is 8 or 12ethylene glycol units, as extenders. The structures for peptidescontaining one to four L-Arg groups (1-Arg, 2-Arg, 3-Arg and 4-Arg) areshown in FIG. 1(a). All were produced and utilized as TFA salts.

CDEX was activated for amino-PEG-peptide coupling by CDI reaction. CDEX(210 mg, 3.0 μmoles) was dried by vacuum evaporation from anhydrouspyridine (2×5 mL), then dissolved in 10 mL anhydrous DMSO. Freshlyopened CDI (36 mg; 220 μmoles) in 1 ml DMSO was added dropwise andstirred for 4 hours at 40° C. The CDEX-Im thus formed was dialyzedagainst water overnight at 4° C. and lyophilized, giving 169 mg product.Nuclear magnetic resonance estimated 58 imidazole groups attached perparticle (assuming one 70-kDa dextran molecule forms one CDEX particle).

Peptides were coupled as carbamate to the above CDEX-Im particles asfollows: 5 mg of the above CDEX-Im (3.8 moles imidazolyl) was dissolvedin 0.5 mL water, and pH was then adjusted to 8.0 with NaHCO₃. Peptide(3.5 μmoles) dissolved in 0.2 mL of DMF was stirred into the CDEX-Imsolution and reacted overnight at 25° C. after which excess Im-wasquenched by additional overnight reaction with 4 μl (50 μmoles) ofethanolamine. For each batch, a parallel batch (7 mg CDEX-Im) wasreacted overnight with 0.1 mg amino-rhodamine (a-Rh) before quenchingwith ethanolamine, giving pink colored conjugate. Conjugates wereexhaustively dialyzed against water at 4° C., then lyophilized. Theproduct was re-dissolved in water to a concentration of about 0.4 mg/mLand then sterile filtered through 0.2 μm syringe filter.

For fluorescence monitoring a small volume of a-Rh-tagged conjugate wasmixed with final concentrated stocks of un-tagged conjugate (1-20 mg/ml)so that their Absorbance at 551 nm was 0.1-0.15. Linkable fluorescencetag was synthesized by modification of Rhodamine isothiocyanate with a3-fold excess of 2,2′-(ethylenedioxy) bis (ethylamine) and purified bycolumn chromatography on silica gel using a stepwise gradient ofmethanol in dichloromethane.

3. Characterization of Physical and Chemical Properties

Peptide concentration was estimated by BCA (Pierce) protein assayagainst a standard curve of free peptide. Zeta potential and size wasmeasured on non-rhodamine product using electrophoretic light scatteringand dynamic light scattering, respectively (Zetasizer, Malvern). The Zaveraged particle size is 15 nm and the full width at half maximum ofthe distribution peak is 24 nm. Zeta potentials for 1-Arg, 2-Arg, 3-Argand 4-Arg peptide conjugates were 0.07 mV, 2.2 mV, 4.6 mV and 9.2 mVrespectively (Table 2).

TABLE 2 Physical and chemical properties of nanoparticle carriers.Peptides per Zeta potential Conjugate particle* Diameter [unit]CDEX-1Arg 19 100 nm 0.07 CDEX-2Arg 28 100 nm 2.2 CDEX-3Arg 23 100 nm 4.6CDEX-4Arg 19 100 nm 9.2

4. Ex Vivo Diffusion Rate Measurements in Rodent Vitreous

4.1. Mathematical Model

The rat ocular lens occupies almost two-third of the rat eyeball volume.Rat vitreous body is in a crescent shape and could be roughly consideredas a two-dimensional structure [7]. We used a two-dimensional model tocalculate the diffusion rate. Assuming right after injection, the drugis uniformly distributed in a circle with a diameter of h, theconcentration distribution in cylindrical coordinates is [8]

$\begin{matrix}{{C = {\frac{1}{2}{C_{0}\left( {{{erf}\frac{\; {h - x}}{2\sqrt{Dt}}} + {{erf}\frac{\; {h + x}}{2\sqrt{Dt}}}} \right)}}},} & (1)\end{matrix}$

where x is the distance from the origin, t is time, C is theconcentration at location x at time t, C₀ is the initial concentration,D is the diffusion rate and erf is the error function.

4.2 Preparation of Fresh, Intact Rat Vitreous Gels

Rat (Long-Evans, Charles River) eyeballs were enucleated immediatelyafter euthanasia. We carefully removed conjunctive tissues and placedthe eyeballs in a home-made concave holder (6 mm in diameter) with pupilfacing up.

Vitreous body is very fragile. Vitreous collagen fibers are tightlylinked to both the anterior segment and retina tissues. Vitreous tendsto liquefy when removed from the eyeball due to collapse of collagenfibers. To maximally preserve the structure of vitreous, we only removedthe cornea and iris for monitoring. We first made a small incision atcorneal limbus using a scalpel blade, circumferentially cut along thelimbus using a scissor, and separated cornea from sclera. We thencarefully picked out iris using a small tweezer. To cancel the dioptricpower of the ocular lens, we added a coverslip on top of the openedeyeball. A tiny amount of water was added between coverslip and ocularlens. A ring spacer was used to hold the coverslip from pressing the eyeball.

4.3 Diffusion Rate Measurements

The opened eyeball with the coverslip was placed under a stereomicroscope (SMZ1500, Nikon) equipped with a high-sensitive CCD (PixelFlyqe, PCO AG, Germany) and a long pass optical filter (FEL0550, Thorlabs;cut-off wavelength: 550 nm) for fluorescence imaging. Two microliter ofnanoparticle colloidal gel was injected to the center of vitreous by amicroliter syringe (Hamilton, 30G needle). Nanoparticles carrying fourdifferent peptides were separately injected and monitored to determinethe influence of various peptide's Zeta potential on the rate ofdiffusion.

We excited Rhodamine labels using a continuous-wave 532 nm laser (10 mW)and recorded the fluorescence distribution every 5 min. We estimated thefluorescence diffusion area (edge defined as e⁻¹ of the centerfluorescence intensity) at each time point, and numerically fitted thearea to a diffusion equation [8]. For each measurement, the preparationand monitoring was completed within 3 hours. The eyeballs were stored inice during transportation, and recovered to room temperature beforeinjection and monitoring.

For each measurement, the preparation and monitoring was completedwithin 3 hours. The eyeballs were stored in ice during transportation,and recovered to room temperature before injection and monitoring.

5. In Vivo Half-Life Measurements

5.1 Intravitreal Injection

Adult rats (250-g Sprague Dawley, Charles River Laboratories) were usedfor in vivo measurements. Before intravitreal injection, animals wereanesthetized by an intraperitoneal injection of a mixture of ketamineand xylazine (ketamine: 11.45 mg/mL; xylazine: 1.7 mg/mL, in saline; 10mL/kg body weight).

We used a microliter syringe with a 30G needle (Hamilton) to performintravitreal injections. The anesthetized rats were placed under astereomicroscope. We inserted the needle to the posterior chamber fromlimbus, and held the syringe still. We push the syringe until solutionwas completely injected to the posterior chamber, and then gentlywithdrew the needle. Lubricating ophthalmic ointment was applied to eyesafter injection.

We intravitreally injected nanoparticle carriers loaded with thecationic peptides of 1-Arg, 2-Arg, 3-Arg and 4-Arg to study therelationship between nanoparticle Zeta potential and its half-life. Theinjection dose was 1.5 μL, about 2.7% of rat's total vitreous volume[9]. Phosphate-buffered saline of the same volume was injected in thecontrol group.

5.2 Fundus and Fluorescence Imaging

Fundus and fluorescence images were taken every three days in thefollowing week after injection and every 7 days after the first week.Animals were anaesthetized by a mixture of isoflurane and air (2%isoflurane at 3 L/min for 10 minutes and 1.5% at 2 L/min in followingexperiments). The rat eyes were anesthetized using a drop of 0.5%Tetracaine Hydrochloride ophthalmic solution and dilated using a drop of1% Tropicamide ophthalmic solution. During imaging, animals were placedon a homemade animal holder. Artificial tears were applied every 2 minto keep the cornea moist.

We took fundus reflectance images to locate the region of interestthrough retinal landmarks, immediately followed with fluorescence imagesusing a customized high-resolution rodent fundus camera [9]. Thereflectance fundus images were taken using a narrow spectral-bandillumination (Halogen lamp with band-pass filter; bandwidth: 12.7 nm,center wavelength: 580 nm) to minimize chromatic aberrations. Forfluorescence imaging, a 532-nm continues-wave laser was combined intoillumination optical path by a 45-degree laser-line mirror. A 550-nmlong pass filter (EdmundOptics) was added before the camera to block theexcitation light, and let the fluorescence and reflected light to pass.The system's optical resolution was 10 μm. The field of view was 50degrees. The light powers of reflectance imaging illumination and laserexcitation were 0.2 mW and 0.25 mW, respectively, which were below thesafety threshold. The exposure times were 0.2 s for fundus imaging and 2s for fluorescence imaging. All experiments were performed in compliancewith the ARVO Statement for the Use of Animals in Ophthalmic and VisionResearch and were approved by the Animal Care and Use Committee ofNorthwestern University.

6. Histological Examination

Rats with no fluorescence detected for two weeks, or 8 months afterintravitreal injection (if the fluorescence signal didn't fade away)were euthanized, eyes were enucleated, and immediately fixed in formalinand prepared for histological evaluations. Paraffin sections werestained with hematoxylin/eosin and examined for structural abnormalitiesand signs of inflammatory infiltrations in masked fashion.

Results

1. Ex Vivo Diffusion Rate In Vitreous

The ex vivo nanoparticle diffusion with time are shown in FIG. 2(a), andthe calculated diffusion rates are shown in FIG. 2(b). Diffusion rate of4-Arg particles (ζ+9.2 mV) are not shown due to the difficulties ofmeasuring the extremely slow particle movement during the observationperiod. In order to minimize the influence from initial injectionconditions, we used relative area changes to calculate diffusion rates.(See supplementary information for more details.)

Nanoparticle surface modified with peptides containing 1, 2, or 3Arginine groups had distinct diffusion behaviors where nanoparticlesmodified with 1-Arg peptides (ζ+0.07 mV) expanded the fluorescent areaquickly, 3-Arg peptide modified nanoparticles (ζ4.6 mV) only diffusedminimally in one hour, and the diffusion of 2-Arg peptide modifiednanoparticles (∂2.2 mV) was intermediate. The calculated diffusioncoefficients for 1-Arg, 2-Arg, or 3-Arg peptide modified nanoparticleswere 7.6×10⁻⁹ cm²/s, 2.7×10⁻⁹ cm²/s and 3.0×10⁻¹° cm²/s, respectively.The diffusion coefficient of 3-Arg nanoparticles was below themeasurement error, since the nanoparticles barely moved in one hour.Longer monitoring time will be needed for more accurate estimation ofits diffusion. Compared with the theoretical diffusion coefficient ofuncharged particles, the diffusion coefficients of the fabricatednanoparticles was significantly reduced. Ideally, the diffusioncoefficient of 50-nm nanoparticles in water is about 1×10⁻⁷ cm²/s.Considering the viscosity of vitreous is three times larger than that ofwater, the diffusion coefficient of 50-nm nanoparticles in vitreousshould be 2.5×10⁻⁸ cm²/s. Compared with this value, 1-Arg modifiednanoparticles had a clear effect in reducing the diffusion rate of thecarriers by at least 3 fold, while the diffusion coefficient of 2-Argand 3-Arg nanoparticles were significantly reduced by one and two ordersof magnitude. The 2-Arg nanoparticles were comparable to un-modifiedparticles with a diameter of 450 nm, and 3-Arg nanoparticles werecomparable to micron-scale particles in terms of diffusion coefficient.The diffusion coefficients were inversely proportional to the Zetapotential of peptide modified nanoparticles, suggesting that the ionicinteraction is responsible for reduced particle diffusion.

We confirmed the ionic binding between nanoparticles and hyaluronic acidmolecules by competitive binding. We injected the mixture of thenanoparticles and protein molecules with a high Zeta potential(protamine, >20 Arg/35 kD monomer) to the vitreous ex vivo, andmonitored the particle diffusion. Protein molecules carrying positivecharge can competitively bind to hyaluronic acid. Such competitivebinding will increase the nanoparticles' diffusion if nanoparticles arealso ionically bound to hyaluronic acid, but will minimally affect thediffusion if the previously observed reduction of nanoparticle diffusionwas caused by the trapping of collagen fiber network. In the competitionbinding assay, we observed significant increases in the nanoparticlediffusion, confirming the ionic biding between the nanoparticles andhyaluronic acid.

2. In Vivo Half-Life Measurement

Examples of the nanoparticle fluorescent maps overlaid with fundusimages are shown in FIG. 3. The fluorescence intensities were uniformlynormalized by the peak intensity of fluorescence of 3-Arg nanoparticleinjection in day one's observation. As shown in FIGS. 3(a) to 3(c), the1-Arg nanoparticles spread into a 6-mm² area in one day after injection,and 90% of fluorescence signal diminished by day 8. The 2-Argnanoparticles (FIG. 3(d)-3(f)) spread into a 1.7 mm² area, and thefluorescence was detectable up to two months. The 3-Arg nanoparticles(FIG. 3(g)-3(i)) spread to 1.3 mm², and the fluorescence signal was onlyslightly reduced after 6 months. The behavior of 4-Arg nanoparticles(not shown) are similar to 3-Arg nanoparticles. By comparing thefluorescence locations determined by retinal vasculature, we found thatboth 2-Arg and 3-Arg nanoparticles stayed approximately at the originalsites, which could be in a practical range for targeting lesionstherapeutically. However, the slight changes in location may beattributed to the image angel and eyeball orientation. We estimated thehalf-life of nanoparticles from the decays of integrated fluorescenceintensities. The relative total amount of nanoparticles was estimated byintegrating the fluorescence intensity over the image. The distinctfluorescence intensity decay curves of the three type of nanoparticlesin the first 60 days are shown in FIG. 3.

The corresponding half-lives are shown in FIG. 4(b). The half-life of1-Arg nanoparticles was very short (1 to 5 days), which was comparableto that of some peptides reported in rabbit and human eyes. This mayalso be due to the small volume of rat vitreous which enables facileescape of weakly charged or uncharged nanoparticles. The 2-Argnanoparticles had a moderate half-life (7 to 37 days), thus it couldextend the interval to the subsequent injection by an additional month.The error bars (confidence intervals) of 1-Arg and 2-Arg nanoparticleswere relatively large. This may be attributed to the small sample sizeand individual physiological differences between each animal. We didn'tobtain the half-life of 3-Arg nanoparticles since all animals receivingthese nanoparticle injections showed strong fluorescence at the 240thday, a time at which the animals were terminated, thus, suggesting thehalf-life of 3-Arg nanoparticles in the vitreous is over 240 days.

3. Histological Evaluations

Following the termination of the experiments, animals receiving variousnanoparticles for different durations were sacrificed and their eyeswere subjected to histological evaluation. Representative histologicalimages are shown in FIG. 5. We observed no adverse effects on theintegrity of ocular structure or infiltration of inflammatory cells.

Discussion

We demonstrated the extended residence of surface modified nanoparticlesin vitreous ex vivo and in vivo. We confirmed that such reduceddiffusion originated from the ionic binding between cationic peptidesand anionic molecules in vitreous, which is consistent with the previousstudy [10]. One evidence is that the movement of nanoparticlesmonotonically decreased with increasing Zeta potentials, suggesting theincreased binding strength from high surface ionization. The otherdetermine evidence is that in the competitive binding experiment, ionicbinding between protamine and hyaluronic acid increased the rate ofnanoparticle diffusion. This can be explained by the fact that ournanoparticles anchored themselves to hyaluronic acid by multiply weakionic interactions. Competitive binding by poly-cationic protamineoccupied the hyaluronic acid, causing the increased diffusion ofnanoparticles.

The biocompatibility of the polycationic particles is critical to thepossible clinical applications. To reduce the total toxicity, we usednano-scale particle carriers and low toxic L-Arg cationic groups foranchoring. The small particle size minimizes inflammatory or obstructiveeffects. Since particle anchoring no longer relies on entrapment withinthe vitreous fiber network, the drug carriers are smaller than the meshof collagen fibers, allowing sub-micron sterile filtration and minimizesresidual aggregation on the retina and the likelihood of immuneresponse. Our nanoparticles are smaller than the trabecular drainagemeshwork, and should eventually exit from the eye ball with trabecularoutflow when detached from vitreous Also, dextran has been usedclinically over many years and are safe and readily eliminated [5] viakidney excretion. L-Arg is orders of magnitude safer that most of othercations tested, possibly because cells are able to detoxify L-Arg,through the charge eliminating action of peptide deiminases (PAD), whichare known to be present in retina [11]. Peptide arginine, rather thanother polymeric forms, may be more amenable to detoxification by PAD.However, PAD presence in vitreous may ultimately convert L-Arg tocitrulline on the carrier surface, and limit the residence time. Weobserved no adverse effects on the integrity of ocular structure orinfiltration of inflammatory cells in the histological examination ofrat eyes in three types of nanoparticles.

The half-life of the nanoparticles in vitreous is controlled here byadjusting Zeta potential. Zeta potential characterizes the extent ofsurface ionization, which determines the binding strength and half-lifeof nanoparticles. There are several ways to control Zeta potential: oneis to link peptides with different numbers of positive charged groups.Currently, three discrete Zeta potentials of 0.07, 2.4 and 4.9 resultthree half-lives of 3 days, 22 days and more than 8 months. To adjusthalf-life, we could vary the number of peptides on each nanoparticle. Wecan change the average loading number of 3-Arg peptides or increase2-Arg peptides to continuously adjust the Zeta potential. By varying theabove parameters, we construct versatile drug carriers with a wide rangeof half-lives to fit multiple intra-ocular delivery objectives fordifferent injection interval requirements.

REFERENCES

-   [1] National Eye Institute, Prevalence of Adult Vision Impairment    and Age-Related Eye Diseases in America,    https://nei.nih.gov/eyedata/adultvision_usa, 2016.-   [2] K. G. Falavarjani, Q. D. Nguyen, Adverse events and    complications associated with intravitreal injection of anti-VEGF    agents: a review of literature, Eye, 27 (2013) 787-794.-   [3] Q. G. Xu, N. J. Boylan, J. S. Suk, Y. Y. Wang, E. A.    Nance, J. C. Yang, P. J. McDonnell, R. A. Cone, E. J. Duh, J. Hanes,    Nanoparticle diffusion in, and microrheology of, the bovine vitreous    ex vivo, Journal of Controlled Release, 167 (2013) 76-84.-   [4] B. J. Zern, H. Chu, A. O. Osunkoya, J. Gao, Y. Wang, A    Biocompatible Arginine-Based Polycation, Advanced Functional    Materials, 21 (2011) 434-440.-   [5] I. Wasiak, A. Kulikowska, M. Janczewska, M. Michalak, I. A.    Cymerman, A. Nagalski, P. Kallinger, W. W. Szymanski, T. Ciach,    Dextran Nanoparticle Synthesis and Properties, Plos One, 11 (2016).-   [6] T. H. Senanayake, G. Warren, S. V. Vinogradov, Novel Anticancer    Polymeric Conjugates of Activated Nucleoside Analogues, Bioconjugate    Chemistry, 22 (2011) 1983-1993.-   [7] A. Chaudhuri, P. E. Hallett, J. A. Parker, Aspheric curvatures,    refractive indices and chromatic aberration for the rat eye, Vision    Res, 23 (1983) 1351-1363.-   [8] J. Crank, The mathematics of diffusion, Oxford university press,    1979.-   [9] H. Li, W. Liu, H. F. Zhang, Investigating the influence of    chromatic aberration and optical illumination bandwidth on fundus    imaging in rats, J. Biomed. Opt., 20 (2015) 106010.-   [10] H. Kim, S. B. Robinson, K. G. Csaky, Investigating the movement    of intravitreal human serum albumin nanoparticles in the vitreous    and retina, Pharmaceutical research, 26 (2009) 329-337.-   [11] S. K. Bhattacharya, Retinal Deimination in Aging and Disease,    Iubmb Life, 61 (2009) 504-509.

Example 7—Preparation and Testing of Cholesterol-Dextran Nanoparticleswith Surface-Linked Peptides In Vitreous

Cholesterol-dextran nanoparticles (NP) were labeled with cyanine 7 amine(Cy7) with less than 1 Cy7 per NP. Two types of positively chargedpeptides were linked on the NP surface, load of 61-64 peptides perparticle. (See FIG. 7). As illustrated in FIG. 7, the NP are trapped invitreous by ionic binding between peptides on the NP surface andhyaluronic acid polymer in the vitreous.

The reaction conditions used for preparing the NP and the physicalcharacteristics of the NP are provided in Table 3.

TABLE 3 Reaction Condition and Physical Characteristics of theNanoparticles (NP). A NP pNP excess per CDEX pNP/CDEX Pept excess perCDEX Cy7 excess per CDEX CDEX-Cy7 1,400 70 0 5 CDEX-2R-Cy7 1,400 167 2005 CDEX-3R-Cy7 1,400 144 200 5 B NP Yield (%_(w/w)) Particle size (nm) ζ(mV) Pept/CDEX Possitive charge/CDEX Cy7/CDEX CDEX-0-Cy7 51.42 152.27 ±2.20  −0.61 ± 0.08  0 (0) 0 (0) 0.16 CDEX-2R-Cy7 81.29  85.21 ± 14.983.88 ± 1.15 62 (64) 124 (128) 0.24 CDEX-3R-Cy7 91.30 81.69 ± 7.44 6.34 ±1.28 67 (61) 201 (183) 0.28 A: Conditions for the activation of CDEXwith 4-nitrophenyl chloroformate (pNP) and conjugation of peptides(Pept) and dye (Cy7) to the nanocarrier. B: Characterization andmeasurement of the NP by dynamic light scattering and electrophoreticmobility (n = 3). Number of peptides per particle of CDEX; thequantification of peptide was determine by absorbance of tyrosine(EC_(Tyr) = 1,100 M⁻¹cm⁻¹) and BCA (result in brackets and bold). Numberof molecules of Cy7; the quantification of cyanine 7 was determine alsoby absorbance (EC_(Cy7) = 199,000 M⁻¹cm⁻¹).

The UV-VIS spectrum for CDEX-peptide-Cy7 nanoparticles, which contain atyrosine residue, and for CDEX peptide-Cy7 exhibits an absorption peakat about 275 nm (peptide tyrosine) and also exhibit an absorption peakat >700 nm. The fluorescence emission signal observed in the in vivorabbit experiment described below corresponds to the long wavelengthabsorption peak of Cy7, excited at 745 nm in the IVIS instrument.

Retention of the NP in vitreous was tested in vivo in rabbits. 25 μl ofCDEX70-2R-Cy7 (SEQ ID NO:4) 3 mg/ml or CDEX70-3R-Cy7 (SEQ ID NO:5) 3mg/ml was administered by intravitreal injection and imaged via an IVISscan after 4 weeks and nine weeks. Left: 4-week experiment. (See FIG.9). The in vivo diffusion dependent loss of NP from rabbit vitreousexpressed as percentage of the first measurement at day 10post-injection (taken as day 0) is provided in FIG. 10. The determinedhalf-lives of the NP is as follows: CDEX-0-Cy7: 4 days; CDEX-2R-Cy7: 7days; CDEX70-3R-Cy7: 13 days. In vivo diffusion-dependent loss of NPfrom rabbit vitreous expressed as Flux of the first measurement at day10 post-injection (taken as day 0) of CDEX70-2R-Cy7 at 4 differentconcentrations [Control: 0 mg/ml (n=6). 3 mg/ml (n=3). 6 mg/ml (n=2) and12 mg/ml (n=2)] is provided in FIG. 11. The sample at 12 mg/ml wasobserved to be eliminated faster than other concentrations which mightbe because the retention capacity of hyaluronic acid was exceeded.

In the foregoing description, it will be readily apparent to one skilledin the art that varying substitutions and modifications may be made tothe invention disclosed herein without departing from the scope andspirit of the invention. The invention illustratively described hereinsuitably may be practiced in the absence of any element or elements,limitation or limitations which is not specifically disclosed herein.The terms and expressions which have been employed are used as terms ofdescription and not of limitation, and there is no intention that in theuse of such terms and expressions of excluding any equivalents of thefeatures shown and described or portions thereof, but it is recognizedthat various modifications are possible within the scope of theinvention. Thus, it should be understood that although the presentinvention has been illustrated by specific embodiments and optionalfeatures, modification and/or variation of the concepts herein disclosedmay be resorted to by those skilled in the art, and that suchmodifications and variations are considered to be within the scope ofthis invention.

Citations to a number of patent and non-patent references are madeherein. The cited references are incorporated by reference herein intheir entireties. In the event that there is an inconsistency between adefinition of a term in the specification as compared to a definition ofthe term in a cited reference, the term should be interpreted based onthe definition in the specification.

We claim:
 1. Nanocarriers that are biodegradable or that can be excretedand have a net positive surface charge and zeta potential between about+2 to about +20 mV, wherein the net positive surface charge is providedby peptides that are covalently attached to the surface of thenanocarriers.
 2. The nanocarriers of claim 1, wherein the nanocarrierscomprise a polymeric carbohydrate and are transparent, and preferablyhave a diameter that permits for filter sterilizing.
 3. The nanocarriersof claim 1, wherein the nanocarriers comprise dextran which optionallyis a condensed dextran hydrogel, chitosan, pullulan, or a dendrimer. 4.The nanocarriers of claim 1, wherein the peptides comprise C-terminalamide groups.
 5. The nanocarriers of claim 1, wherein the peptidescomprise at least 2 amino acids and no more than 11 amino acids.
 6. Thenanocarriers of claim 1, wherein the amino acid sequence of thecovalently attached peptides includes at least 2 L-Arginine residues, nomore than 4 L-Arginine residues, and no other charged amino acids otherthan L-Arginine residues, and where the amount of covalently attachedpeptides produces a positive average zeta potential of the particlesranging from about +2 to about +20 mV.
 7. The nanocarriers of claim 1,wherein the amino acid sequence of the attached peptides comprises anamino acid sequence of a human protein that is secreted into theextracellular matrix or that is found in vitreous humor, blood, urine,or saliva, or has an amino acid sequence that is at least 75% identicalwith the corresponding sequence from the human protein that is secretedinto the extracellular matrix or that is found in vitreous humor, blood,urine, or saliva.
 8. The nanocarriers of claim 1, wherein the peptidesinclude at their N-terminus a neutral amino acid residue selected fromthe group consisting of sarcosine, or beta-alanine.
 9. The nanocarriersof claim 1, wherein the peptides are covalently attached to thenanocarriers via conjugation between hydroxyl groups on the surface ofthe nanocarriers and free amino groups N-terminally linked to thepeptides the peptides.
 10. The nanocarriers of claim 1, wherein thepeptides are covalently attached to the surface of the nanocarriers viacarbamate conjugation between hydroxyl groups on the surface of thenanocarriers and an amino group appended to the peptide N-terminus,wherein the amino group is selected from the group consisting of a freealpha amino group on the peptides, a free beta, gamma, delta or epsilonamino acyl group on the peptides, as in epsilon aminocaproic acid, anamino-PEG(4-12) acyl amide of the peptide N-terminus, or a3-pyrrolidyl-3-carboxylate amide an amino-PEG(4-12) acyl amide of thepeptide N-terminus.
 11. The nanocarriers of claim 1, wherein thepeptides are covalently attached to the surface of the nanocarriers viaamide conjugation between carboxyl groups on the surface of thenanocarriers and an amino group appended to the peptide N-terminus,wherein the amino group is selected from the group consisting of a freealpha amino group on the peptides, a free beta, gamma, delta or epsilonamino acyl group on the peptides, as in epsilon aminocaproic acid, or anamino-PEG(4-12) acyl amide of the peptide N-terminus.
 12. Thenanocarriers of claim 1, wherein the peptides have a formula:B-Z-AA0-(AA1)_(n)-Y, where n is an integer between 1 and 10 where noless than two AA and no more than 4 AA are L-arginine, and all other AAare neutral (not lysine or glutaric acid or aspartic acid). wherein: Bis present or absent, and when B is present, B is selected from thegroup consisting of amino-n-butoxy, amino-ethoxyethyloxy,amino-piperidyl (3, or 4)-oxy, amino-pyrrolidinyl (3)-oxy, amino-benzyl(3, or 4)-oxy, aminoethylamido-valeric acid (4)-oxy, amino-cyclohexyl(3, or 4)-oxy, and amino-cyclopentyl (3)-oxy; Z is absent or present,and when Z is present, Z is a dicarboxylic acid, including suberic,adipic, glutaric, dimethylglutaric, succinic in half amide bond to AA0or AA1, where the OH group of an above amino alcohol, B is bonded as anester to the free dicarboxylic acid group in half-amide linkage to orAA1; AA0 is present or absent, and when present, AA0 is selected fromthe group consisting of L-arginine, a naturally occurring amino acidwith an uncharged side chain (e.g., sarcosine and glycine),beta-alanine, and L-proline; AA1 is L-arginine or a naturally occurringamino acid with an uncharged side chain; Y is an amide, amono-substituted or di-substituted alkyl amide (e.g., methylamide,ethylamide, and dimethylamide), or a PEG (4-12) amide; with the provisothat: the peptides have a net positive charge and their multiple linkageto carrier produces nanoparticles having zeta potential between about +2to about +20 mV; when peptide comprises from about 10% to about 50% ofthe conjugate mass, whereby ester hydrolysis slowly reduces peptidecontent and zeta potential of the nanoparticle, leading to acceleratingvitreal loss.
 13. The nanocarrier of claim 12 in which the appendedesterified dicarboxypeptide [Z-AA0-(AA1)_(n)-Y], comprising from about10% to about 50% of the total nanocarrier mass, is bio-active, as inanti-angiogenic peptide adipic-Sar-Tyr-Asn-Leu-Tyr-Arg-Val-Arg-Ser-amide(SEQ ID NO:6), thus acting simultaneously as a prodrug as well as ananchor to slow diffusion.
 14. The nanocarriers of claim 12, wherein B isan amino-PEG-carboxylic acid having between 4 and 12 ethylene glycolunits in amide bond to AA0 or AA1, and Z is absent.
 15. The nanocarriersof claim 1 in which amino-PEG-OH or amino-PEG-OMe of molecular weightranging from 200 to 2,000 grams/mole are additionally appended tocarriers through carbamate or amide bonds while comprising from about10% to about 50% of the conjugate mass.
 16. The nanocarriers of claim 1,wherein the peptides are selected from the group consisting of:NH₂-PEG(8-12)-CO-Gly-Val-Ile-Thr-Arg-Ile-Arg-NH₂ (SEQ ID NO:1);NH₂-PEG(8-12)-CO-Arg-Arg-Ser-Ser-Arg-Arg-Trp-NH₂ (SEQ ID NO:3);NH₂-PEG(8-12)-CO-Tyr-Arg-Val-Arg-NH₂ (SEQ ID NO:4);NH₂-PEG(8-12)-CO-Arg-Arg-Tyr-Arg-Leu-NH₂ (SEQ ID NO:5);NH₂-PEG(8-12)-CO-Arg-Arg-Ser-Ser-Arg-Arg-NH₂ (SEQ ID NO:9); and theN-terminal amino group is in covalently linked to a hydroxyl on thesurface of the particles through an amide linkage or carbamate linkage.17. The nanocarriers of claim 1, wherein the peptides are selected fromthe group consisting of:3-pyrrolidine-CONH-PEG(8)-CO-Tyr-Arg-Val-Arg-Ser-NH₂ (SEQ ID NO:4); and3-pyrrolidine-CONH-PEG(8)-CO-Arg-Arg-Tyr-Arg-Leu-NH₂ (SEQ ID NO:5). 18.The nanocarriers of claim 12, wherein the appended esterifieddicarboxypeptide [B-Z-AA0-(AA1)_(n)-Y] comprising from about 10% toabout 50% of the total nanocarriers mass is pyrrolidinyl(3)-oxy-adipic-Sar-Tyr-Asn-Leu-Tyr-Arg-Val-Arg-Ser-amide (SEQ ID NO:6).19. A pharmaceutical composition comprising the nanocarriers of claim 1and a suitable pharmaceutical carrier.
 20. A method comprisingadministering the pharmaceutical composition of claim 19 to a subject inneed thereof.